Pulsed-multiline excitation for color-blind fluorescence detection

ABSTRACT

The present invention provides a technology called Pulse-Multiline Excitation or PME. This technology provides a novel approach to fluorescence detection with application for high-throughput identification of informative SNPs, which could lead to more accurate diagnosis of inherited disease, better prognosis of risk susceptibilities, or identification of sporadic mutations. The PME technology has two main advantages that significantly increase fluorescence sensitivity: (1) optimal excitation of all fluorophores in the genomic assay and (2) “color-blind” detection, which collects considerably more light than standard wavelength resolved detection. Successful implementation of the PME technology will have broad application for routine usage in clinical diagnostics, forensics, and general sequencing methodologies and will have the capability, flexibility, and portability of targeted sequence variation assays for a large majority of the population.

CROSS REFERENCE TO RELATED APPLICATION

This application is a divisional of co-pending U.S. patent applicationSer. No. 11/248,910, filed Oct. 12, 2005, which is a continuation ofU.S. patent application Ser. No. 09/941,165, filed Aug. 28, 2001, whichissued as U.S. Pat. No. 6,995,841 on Feb. 7, 2006, the contents of whichapplications are incorporated herein by reference in their entirety.

BACKGROUND OF THE INVENTION

I. Field of the Invention

The present invention relates generally to the fields of high throughputgenetic analysis applications and fluorescence spectroscopy. Moreparticularly, it provides a variety of compositions and methods for usein high-throughput DNA sequence identification.

II. Description of Related Art

The Human Genome Project (HGP) holds tremendous promise for discoveriesof the molecular mechanisms that trigger the onset of many commondiseases over the next several decades. The initial HGP goals underwaywill provide or have provided the complete and accurate genome sequencesof human and multiple well-studied genetic model organisms, such asmouse, rat, fruit fly, nematode, yeast and numerous bacteria. From thisfoundation of reference genome sequences, the elucidation of completegene sets, coupled with comparative cross-species studies, are expectedto assist significantly in the assignment to specific human genes ofprotein function and disease associations. Other technologies complementthe assignment of biological functions: gene and protein expressionprofiling, mouse gene-knockouts, and techniques that measureprotein-protein interactions. The elucidation of gene structure-proteinfunction relationships are key to understanding how genomic sequencevariation between individuals can cause increased risk or predispositionto certain complex diseases or are even the etiologic agents responsiblefor the onset of particular diseases. However, the use of geneticvariation in clinical practice is only beginning and technology tofacilitate its use is greatly needed.

The most commonly observed form of human sequence variation is singlenucleotide polymorphisms (SNPs), which occur at a frequency ofapproximately 1-in-300 to 1-in-1000 base pairs. In general, 10%-to-15%of SNPs will affect either protein function by altering specific aminoacid residues, or will affect the proper processing of genes by changingsplicing mechanisms, or will affect the normal level of expression ofthe gene or protein by varying regulatory mechanisms. Several recentexamples are the associations of mutations with the NOTCH4 gene andschizophrenia (Wei et al., 2000), peroxisome proliferator-activatedreceptor gamma (PPARγ) gene and severe insulin resistance (Deeb et al.,1998), and melanocortin-4 receptor (MC4R) gene and inherited obesity(Yeo et al., 1998).

The identification of informative SNPs will lead to more accuratediagnosis of inherited diseases, better assessment of risksusceptibilities, and could be assayed in specific tissue biopsies forsporadic mutations. An individual's SNP profile could be used to offsetand significantly delay the progression of disease by helping in thechoice of prophylactic drug therapies. A SNP profile of drugmetabolizing genes could be used to prescribe a specific drug regimen toprovide safer and more efficacious results. To accomplish goals likethese, genome sequencing will move into the resequencing phase of notjust a handful of individuals, but potentially the partial sequencing ofmost of the population. Resequencing simply means sequencing in parallelspecific regions or single nucleotides that are distributed throughoutthe human genome to obtain the SNP profile for a given complex disease.

For this technology to be applicable and practicable for routine usagein medical practice, it must be robust, easy-to-use, highly sensitive,flexible, portable, and the results should be accurate and rapidlyobtained. While current technologies at large genome centers are robustand results are accurate, they are inadequate and inflexible forresequencing millions of individuals in routine clinical practice. It istherefore advantageous to develop a DNA sequencing instrument, whichmeets these needs. Miniaturization of this technology is alsoadvantageous because smaller instruments potentially require less sampleand reagents and can be more readily transported and located in areassuch as clinics or doctors' offices.

Ideally, DNA sequencing technology would have the sensitivity for directassays without DNA amplification, and be simple and portable for routineusage in basic, applied, and clinical laboratories. Currently, DNAsequencing technology for high-throughput analyses are specialized andcentralized in large genome centers and require numerous molecularbiology manipulations that take days or weeks of preparation before DNAsequence analysis can be performed. Thereafter, the state-of-the-arttechnology involves the attachment of four different fluorescent dyes orfluorophores to the four bases of DNA (i.e., A, C, G, and T) that can bediscriminated by their respective emission wavelengths, theelectrophoretic separation of the nested set of dye-labeled DNAfragments into base-pair increments, and the detection of the dyefluorescence following irradiation by a single argon-ion laser source.Current instrumentation for electrophoretic separation comprises a96-capillary array that disperses the different fluorescent signalsusing a prism, diffraction grating, spectrograph, or other dispersingelement and images the four colors onto a charged-coupled device (CCD)camera. The throughput of each 96-capillary instrument is approximately800 DNA samples per day, and the success of the HGP in large-scalegenomic sequencing has been attributed to the use of hundreds of thesemachines throughout the world. The main disadvantages of the currenttechnology are the laborious cloning or amplification steps needed toprovide sufficient DNA material for analyses, the relatively large sizeof the instruments (roughly the size of a 4-foot refrigerator), and theinadequate sensitivity of detection (i.e., inefficient excitation offluorescent dyes with absorption maxima far from the laser excitationwavelength).

Although the resolution of spectral emission wavelengths is themainstream technology used in commercial and academic prototypeinstruments, several groups have explored other physical properties offluorescence as a method for discriminating multicolor systems for DNAsequence determination. Recently, Lieberwirth et al. (1998) described adiode-laser based time-resolved fluorescence confocal detection systemfor DNA sequencing by capillary electrophoresis. In this system, asemiconductor laser (630 nm) was modulated using a tunable pulsegenerator at a repetition rate of 22 MHz (454 psec pulses) and focusedby a microscope objective. The fluorescence was collected by the sameobjective and imaged on a single photon counting module APD (Lieberwirthet al., 1998).

The Luryi group at SUNY Stony Brook have proposed a multiple laserexcitation approach using different radio frequency (RF) modulations anddemodulations to discriminate a mixture of fluorophores (U.S. Pat. Nos.5,784,157 and 6,038,023). U.S. Pat. No. 5,784,157 describes a 4-laserbased fiber optic single capillary monitoring device, which initiallyhas a non-wavelength component, but later the invention discusses thecoupling of spectral resolution for fluorophore discrimination. Thereare three significant flaws apparent in this system relating to theenhanced fluorescence cross-talk and laser scattered light, lowsensitivity detection, and a system that does not appear to scale beyondone capillary.

As described, the target capillary is illuminated simultaneously by allfour lasers, which are modulated by different RF signals. The differentRF signals for all of the dyes are summed together and the detectorphotodiodes are demodulated by additional heterodyne RF signals.Interestingly, Gorfinkel and Luryi describe the creation of Braggreflectors to eliminate cross-talk modulation for a given dye set.Fluorescence cross-talk, however, will not be eliminated using thistechnique. Signal from the “wrong” dye, which is weakly excitedoff-resonance by a particular laser, will be encoded with thecorresponding “wrong” frequency, decoded, and added to the signal forthe target dye. Moreover, scattered laser light will also be modulated,and is likewise not rejected by the heterodyne detection.

The simultaneous multi-modulation method also has a serious shortcomingfor the detection of low light levels, which is a specific aim of thecurrent invention. All the lasers are proposed to operatesimultaneously, followed by detection of substantially all of the entirefluorescence, and conversion of the collected fluorescence to anelectrical signal. This design potentially creates a correspondinglyhigh quantum statistical noise level, which should be distributed to allthe detectors. The demultiplexing process of RFs does not remove thisexcessive random noise, even if the corresponding signal is small(Meabum, 1976). In comparison, the Pulse-Multiline Excitation (PME)system described in the current invention exhibits noise levels inproper proportion, so that a weak signal originating from a particularlaser pulse has a correspondingly low detected noise level during thatlaser's sub-cycle. Optimizing the optical system for producing low noiselevels is essential in establishing the optimum contrast between thepresence and absence of a given dye.

Finally, U.S. Pat. No. 5,784,157 describes a rather complicated array ofoptical fibers, combiners, splitters, and 4 heterodyne detectors withtheir associated spectral filters for a single capillary channel.Scaling this system to a 2-capillary system would entail doubling thementioned detector components. Unfortunately a CCD camera is not readilyadapted for high frequency RF modulation, as it is an “inherentlydiscrete-time” device. In a more recent document. U.S. Pat. No.6,038,023, the multiplicity of spectral filters has been replaced with adispersing prism spectrometer and a high speed one dimensional arraydetector for use with a single capillary channel device; the potentialto scale up to a capillary array system is more feasible as discussed bythe Luryi group, but may require a multiplicity of such spectrometerunits.

The current invention comprises a novel fluorescence device, which iscapable of significant improvements in the limit of detection ofmulti-color fluorescence reactions and may be applied to directmeasurement of such reactions from biological sources (i.e., without theneed for PCR or cloning amplifications). Moreover, this technology,called Pulse-Multiline Excitation or “PME” can be configured on a smallwork surface or in a small instrument, compared to the current DNAsequencing instruments. Thus, a DNA sequencer the size of a suitcase orsmaller is described.

The development of improved DNA sequencing chemistries will likelyimprove the number of independent assays that can be run in parallel.This technology will have broad application in both general sequencingand forensic applications.

SUMMARY OF THE INVENTION

Thus, the present invention contemplates an apparatus and method for usein high-throughput DNA sequence identification. An aspect of theinvention is a pulse-multiline excitation apparatus for analyzing asample containing one or more fluorescent species, comprising: one ormore lasers configured to emit two or more excitation lines, eachexcitation line having a different wavelength; a timing circuit coupledto the one or more lasers and configured to generate the two or moreexcitation lines sequentially according to a timing program to producetime-correlated fluorescence emission signals from the sample; anon-dispersive detector positioned to collect the time-correlatedfluorescence emission signals emanating from the sample; and an analyzercoupled to the detector and configured to associate the time-correlatedfluorescence emission signals with the timing program to identifyconstituents of the sample.

The detector and the analyzer may be integral. In one embodiment, thetwo or more excitation lines intersect at the sample, or the two or moreexcitation lines may be configured so that they do not intersect in thesample. The two or more excitation lines may be coaxial.

In one embodiment of the invention, the apparatus may further comprisean assembly of one or more prisms in operative relation with the one ormore lasers and configured to render radiation of the two or moreexcitation lines substantially colinear and/or coaxial.

The apparatus may have 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14,15, 16 or more excitation lines having 1, 2, 3, 4, 5, 6, 7, 8, 9, 10,11, 12, 13, 14, 15, 16 or more excitation wavelengths, respectively. Thesample may be comprised in 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13,14, 15, 16, up to 20, up to 24, up to 28, up to 36, up to 48, up to 64,up to 96, up to 384 or more capillaries. A sheath flow cuvette may beused.

The timing program may comprise a delay between the firing of each laserof between about 10 fs and about 5 s, between about 1 ms and about 100ms, or between about 50 ps and about 500 ps. One or more of theexcitation lines is pulsed. The pulsed excitation line may be controlledby transistor-transistor logic (TTL) or by mechanical or electronicmeans. In one embodiment, the apparatus may generate a sequence ofdiscrete excitation lines that are time-correlated with the fluorescenceemission signals from the sample.

The lasers may independently comprise a diode laser, a semiconductorlaser, a gas laser, such as an argon ion, krypton, or helium-neon laser,a diode laser, a solid-state laser such as a Neodymium laser which willinclude an ion-gain medium, such as YAG and yttrium vanadate (YVO₄), ora diode pumped solid state laser. Other devices, which produce light atone or more discrete excitation wavelengths, may also be used in placeof the laser. The laser may further comprise a Raman shifter in operablerelation with at least one laser beam. In one embodiment of theinvention, the excitation wavelength provided by each laser is opticallymatched to the absorption wavelength of each fluorophore.

The detector may comprise a charged couple device, a photomultipliertube, a silicon avalanche photodiode or a silicon PIN detector. Thefootprint of the device is preferably small, such as less than 4 ft×4ft×2 ft, less than 1 ft×1 ft×2 ft, and could be made as small as 1 in×3in×6 in.

Another aspect of the current invention comprises a method ofidentifying sample components comprising: (a) preparing a samplecomprising sample components, a first dye and a second dye; (b) placingthe sample in the beam path of a first excitation line and a secondexcitation line; (c) sequentially firing the first excitation line andthe second excitation line; (d) collecting fluorescence signals from thesamples as a function of time; and (e) sorting the fluorescence by eachexcitation line's on-time window, wherein the sample components areidentified. It is an aspect of the invention that the fluorescencesignals are collected from discrete time periods in which no excitationline is incident on the sample, the time periods occurring between thefiring of the two excitation lines. This technique is known as “lookingin the dark.” Yet another aspect of the present invention is that theabsorption maximum of the first dye substantially corresponds to theexcitation wavelength of the first excitation line. The absorptionmaximum of the second dye may also substantially corresponds to theexcitation wavelength of the second excitation line. In yet anotheraspect of the current invention there is a third and fourth dye and athird and fourth excitation line, wherein the absorption maxima of thethird and fourth dyes substantially correspond to the excitationwavelengths of the third and four excitation lines, respectively.Similarly, there may be 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16 ormore dyes wherein the absorption maxima of the dyes substantiallycorresponds to excitation wavelengths of a 5^(th), 6^(th), 7^(th),8^(th), 9^(th), 10^(th), 11^(th), 12^(th), 13^(th), 14^(th), 15^(th),16^(th), or more excitation lines, respectively. The dyes may be azanthene, fluorescein, rhodamine, BODIPY, cyanine, coumarin, pyrene,phthalocyanine, phycobiliprotein, Alexa, squariane dyes, or some othersuitable dye.

In one embodiment of the current invention, the sample components enablethe determination of SNPs. The method may be for the high-throughputidentification of informative SNPs. The SNPs may be obtained directlyfrom genomic DNA material, from PCR amplified material, or from clonedDNA material and may be assayed using a single nucleotide primerextension method. The single nucleotide primer extension method maycomprise using single unlabeled dNTPs, single labeled dNTPs, single3′-modified dNTPs, single base-modified 3′-dNTPs, singlealpha-thio-dNTPs or single labeled 2′,3′-dideoxynucleotides. Themini-sequencing method may comprise using single unlabeled dNTPs, singlelabeled dNTPs, single 3′-modified dNTPs, single base-modified 3′-dNTPs,single alpha-thio-dNTPs or single labeled 2′,3′-dideoxynucleotides. TheSNPs may be obtained directly from genomic DNA material, from PCRamplified material, or from cloned DNA materials and may be assayedusing Sanger sequencing.

In another embodiment of the current invention, analyzing the signals isadapted for the accurate diagnosis of inherited disease, betterprognosis of risk susceptibilities, identification of sporadicmutations, or prescribing tailor-made daily drug regimens for individualpatients. Analyzing the signals may be adapted for routine usage inclinical diagnostics, forensics applications or determining generalsequencing methodologies.

Yet another aspect of the current invention is a method of identifyingsample components comprising: (a) obtaining a biological sample; (b)labeling said sample with one or more fluorophores; (c) separatingcomponents of said sample; and (d) detecting said sample components witha device wherein said device may comprise: one or more lasers configuredto emit two or more excitation lines, each excitation line having adifferent excitation wavelength; a timing circuit coupled to the one ormore lasers and configured to fire the two or more excitation linessequentially according to a timing program to produce time-correlatedfluorescence emission signals from the sample; and a non-dispersivedetector positioned to collect the time-correlated fluorescence emissionsignals; wherein said detector collects time correlated data from saidsample comprising fluorescent emissions of the sample as a result ofirradiation by the one or more excitation lines.

The sample components may be nucleic acids, amino acids or proteins. Theseparation may be by electrophoresis, chromatography or massspectrometry (MS) such as MALDI-TOF, quadrapole mass filter or magneticsector MS. The sample components may be addressed on high density chiparrays.

In one embodiment, the method may further comprise: (e) contacting saidsample components on a surface comprising immobilized oligonucleotidesat known locations on said surface; and (f) performing a singlenucleotide incorporation assay or a mini-sequencing assay. In yetanother embodiment, the method may further comprise rastering saidsurface or said excitation lines such that said excitation lines contactsaid surface at multiple locations.

Another aspect of the current invention is a device comprising: (a) oneor more lasers having two or more excitation lines; (b) one or more beamsteering mirrors wherein said excitation lines each strike said mirrors;(c) a first prism, wherein said two or more excitation lines strike onesurface and exit from a second surface of said first prism; and (d) asecond prism at an angle relative to said first prism, wherein said twoor more excitation lines strike one surface of said second prism afterexiting said first prism and exit said second prism, wherein said two ormore excitation lines are substantially colinear and/or substantiallycoaxial after exiting said second prism. The angle of the second prismrelative to the first prism is dependent on the optical material used.For example, for high dispersion flint glass, the two prisms will bearranged such that the second prism is angled at 45° relative to thefirst prism. For quartz, the angular displacement ranges from 30° to50°.

Another aspect of the current invention comprises a method ofilluminating a sample comprising: (a) steering two or more excitationlines onto a first surface of a first prism; (b) steering two or moreexcitation lines from the second surface of said first prism to a firstsurface of a second prism; wherein said second prism is angled about 45°from said first prism; (c) steering said two or more excitation linesonto a sample after exiting second surface of said second prism, whereinsaid two or more excitation lines are substantially colinear and/orsubstantially coaxial after exiting said second prism.

Yet another aspect of the current invention comprises a method ofcontrolling a sequence of excitation lines comprising: (a) obtaining aTTL circuit comprising an electronic stepper wherein said circuit isoperationally connected to one or more lasers having two or moreexcitation lines; (b) and controlling the sequential firing of the oneor more lasers having two or more excitation lines with a clock pulsefrom the circuit, wherein the frequency of firing one laser isequivalent to the frequency of firing a second laser, but phased shiftedso that one or more lasers having two or more excitation lines can besequentially pulsed. The cycle time of one clock pulse may be from 1μsecond to 5 seconds, or from 100 μsecond to 1 second. The length oftime a first laser produces an excitation line may be similar to thelength of time a second laser produces an excitation line. As usedherein, similar means within 20%, within 10%, or more preferably within5% of the time length. Between 2-to-16, or 2-to-8 excitation lines aresequentially pulsed.

Yet another method of the current invention comprises a method ofcontrolling a sequence of excitation lines comprising: (a) obtaining aTTL circuit comprising an electronic stepper wherein said circuit isoperationally connected to one or more lasers having two or moreexcitation lines; (b) and controlling the sequential firing of the oneor more lasers having two or more excitation lines with a clock pulsefrom the circuit, wherein the frequency of firing a first laser isdifferent from the frequency of firing a second laser. This method maybe used to control 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15 or 16lasers.

BRIEF DESCRIPTION OF THE DRAWINGS

The following drawings form part of the present specification and areincluded to further demonstrate certain aspects of the presentinvention. The invention may be better understood by reference to one ormore of these drawings in combination with the detailed description ofspecific embodiments presented herein.

FIG. 1. An example of a PME device where each laser is regulatedindividually by its own power supply (A). The TTL stepper or clock chipcircuit (FIG. 3) chooses which power supply is turned on at a specifictime as it cycles through the five lasers. The beam steering mirrors (B)allow various degrees of adjustment to align the excitation lines sothat once they go through a dual prism assembly (FIG. 2) (C), they willbecome colinear and/or coaxial. The beams enter the dark box (D) wherescattered light is reduced by the use of irises and a long cell. Thedyes are detected by the photomultiplier tube (E) through a collectinglens. The signals are recorded by the oscilloscope (F) where digitalpictures can be analyzed.

FIG. 2. Inversion dispersion scheme using a dual prism assembly tocombine pulsed multiline excitation laser sources from discretelocations. The beams all enter from the left hitting the prism atvarying angles and positions on the left side of the first prism (upperleft). As they hit the first prism, the laser beams all bendapproximately at a 45-degree angle. At this point the beams are not yetcolinear and/or coaxial but they are spatially closer together thanbefore. As they hit the second prism, they once again hit at varyingangles and positions, and become colinear and/or coaxial as they exitthe prism.

FIG. 3. TTL Circuit Clock Chip (74174). MR, when low, resets the chipand sets all outputs to low; CP is the Clock Pulse Input. Q0 through Q7are outputs that connect to and signal each of up to eight lasers tofire in sequence.

FIG. 4A, FIG. 4B and FIG. 4C. Photographic data from the oscilloscopeoutput. Two channels from the oscilloscope were set to record the clocksignal for firing the red laser (top line) and the PMT detector output(bottom line). Arrows correspond to the red and green laser pulses. Dataon dilute aqueous solutions containing both BODIPY 523/547 and BODIPY630/650 dyes (FIG. 4A), BODIPY 630/650 dye only (FIG. 4B), or BODIPY523/547 dye only (FIG. 4C) were collected.

DESCRIPTION OF ILLUSTRATIVE EMBODIMENTS I. The Present Invention

The present invention describes a novel device and approach tofluorescence detection, which has general application for geneticanalysis methodologies with particular emphasis on DNA sequencingtechnologies and high-throughput identification of single nucleotidepolymorphisms (SNPs). The PME technology has two main advantages thatsignificantly increase fluorescence sensitivity: optimal excitation ofall fluorophores in the genomic assay and “color-blind” detection, whichcollects considerably more light than traditional dispersive detectors.The fluorescence detector can be designed to miniaturize DNA sequencingtechnology with a sensitivity enabling direct detection of fluorescentDNA assays from genomic DNA material. The PME is useful for clinicaldiagnostic, forensic, and general sequencing.

II. Pulsed Multi-line Excitation (PME) Detection

In the current invention, spectral dispersion or wavelengthdiscrimination of fluorescent dyes is eliminated, which increases theamount of fluorescent signal detected. The sequential pulsed-laserexcitation system using multiple lasers emitting specific wavelengths oflight, which are matched for efficient excitation of a given set offluorophores, can determine selectivity and sensitivity. By matching theabsorption maximum of each fluorophore, the PME technology excites eachdye with the highest quantum efficiency, thus considerably reducing therequired sample size (i.e., the number of fluorescent molecules requiredfor detection). At first glance, replacing one laser with four lasersmay appear counterintuitive to miniaturization. New solid state lasers,however, such as diode pumped Nd:YAG sources or diode lasers are muchsmaller (ca. 2″ long) than standard argon ion lasers and are much moreefficient requiring smaller power supplies for operation. For example,the footprint of four solid-state lasers together is approximately20-fold smaller than a single argon-ion laser system. Simply replacingthe argon-ion laser, which for a DNA sequencer relies on two excitationlines at 488 nm and 514.5 nm, with a equal power 532 nm Nd:YAG canreduce the laser size, but would reduce the excitation/emissionintensities of shorter wavelength dyes, and still would not efficientlyexcite longer-wavelength dyes that have absorption maxima far from thelaser wavelengths.

For the PME technology to discriminate four fluorescent dyes, fourexcitation lines are combined by inverse dispersion, which isillustrated but not limited to using a prism assembly or diffractiongrating. The resultant beam would look on average like a “white light”laser beam. However, the solid-state lasers are electronicallycontrolled and are pulsed or fired sequentially as discrete packages ofwavelength specific light. Alternatively, laser sources can be pulsed orfired using a synchronized shutter system. Each dye brightly fluoresceswhen its matched laser source is turned on, while it responds onlyweakly, if at all, to the other three laser pulses. The fluorescencefrom each excitation event is collected using a non-dispersed or “colorblind” method of detection. A non-dispersive detector is a detector inwhich the incident radiation is not separated based on the emissionfluorescence wavelength of different fluorescent dyes. Thus, DNAsequence is determined by the PME technology based on the timecorrelation of detector response to specific wavelengths of excitationlight, and not spectral resolution of emission wavelengths. Switchingthe solid-state lasers on a millisecond timescale is straightforward,hence thousands of 4-laser excitation cycles may be completed in thetime scale for eluting a single base of DNA by capillaryelectrophoresis.

Moreover, an advantage of the non-dispersed system is that the detector(i.e., CCD) collects significantly more light, since the fluorescentlight is directly coupled to the detector. Typically for the current DNAsequencer, a dispersive element requires highly collimated light foreffective wavelength separation. Moving the collection lens closer tothe sample can increase the collected fluorescent light, but collimationis lessened, and spectral selectivity is reduced. Similarly, reducingthe distance between the dispersing element and the detector results inreduced spectral selectivity. For the non-dispersed system, however,moving the collection lens much closer to the sample or to the detectorincreases the collected light, inverse to the square of the distance,but without sacrificing the selectivity that is provided by four lasercycling. Thus, the miniaturization process inherently delivers morefluorescent light to the detector.

Typically, miniaturizing a system incurs inevitable penalties insensitivity and selectivity. For example, fluorescent signal is lost asthe laser source becomes smaller in size and power, and selectivity iscompromised because spectral dispersing elements need physical space toseparate emission wavelengths and compressing the spectrometer portionof the detection sacrifices spectral resolution. Consequently, thesample size is increased to offset these losses, which tends tomarginalize the benefits derived by shrinking the conventionaldispersive optical system. The design described herein minimizes thelosses in downsizing instrumentation, but increases the sensitivityconsiderably by the process of miniaturization. The current inventioncomprises a novel detection system that allows the optical components toact synergistically when miniaturized.

An additional advantage of non-dispersed detection is enhancedsignal-to-noise compared to the current 96-capillary DNA sequencer. Toobtain the wavelength spectrum for each DNA sequence reaction, a largenumber of pixels are read out, and this electronic readout process addsnoise for every pixel read. For the non-dispersed system, all pixelsthat receive light from a particular capillary are “binned” and read outas a single unit, considerably reducing the associated electronic noise.

III. Fluorophores

An advantage of using PME or any time-based detection as opposed towavelength discriminating detection is the increase in the number offluorophores, which can be used. At any given excitation wavelength,there are often only about two or three commercially available dyes thatemit with narrow enough emission bands with sufficiently separatedwavelength maxima that can be individually measured simultaneously (U.S.Pat. No. 6,139,800). If three or more fluorophores can be found, thereis still substantial cross-talk or overlap of the emission spectra thatwill require substantial deconvolution of the spectra with acorresponding increase in the likelihood of error in identifying thespecies.

One solution to this problem has been the addition of a second laser toallow for the simultaneous or sequential detection of up toapproximately six dyes (U.S. Pat. No. 6,139,800). However, this solutionstill has the problem of substantial overlap in the spectra and the needfor signal intensities great enough to be detected after spectraldispersion of the signal.

Optimally, the way to obtain the highest emission signal possible is tooptically match an excitation source with the absorption maxima of a dyewith a high molar extinction coefficient. This is done for everyfluorophore. However, the excitation source need not match theabsorption maxima exactly, instead, it is important to obtain laser-dyecombinations where each dye has an absorption maxima which substantiallycorresponds with one source wavelength with concomitant emission,coupled with minimal absorption/emission (cross-talk) from thenon-matched laser sources used in the assay.

A system with four fluorophores used to detect the 4 DNA bases ispreferred. However, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, or16 different fluorophores may be used with the PME system.

A non-limiting list of dyes that may be used in the current inventioninclude BODIPY dyes (BODIPY 630/650, BODIPY 650/665, BODIPY 589/616 orBODIPY-TR, BODIPY 581/591 BODIPY 523/547 orBODIPY-R6G,5,7-dimethyl-BODIPY (503/512) or BODIPY-FL,1,3,5,7-tetramethyl-BODIPY (495/503), BODIPY-TMR-X or BODIPY(564/570)-X, BODIPY-TR-X or BODIPY (589/616)-X, BODIPY (530/550), BODIPY(564/570), and BODIPY (558/568)), a zanthene dye, a rhodamine dye(rhodamine green, rhodamine red, tetraethylrhodamine, 5-carboxyrhodamine 6G (R6G), 6-carboxy R6G, tetramethylrhodamine (TMR), 5-carboxyTMR or 5-TAMRA, 6-carboxy TMR or 6-TAMRA, rhodamine B, X-rhodamine(ROX), 5-carboxy ROX, 6-carboxy ROX, lissamine rhodamine B, and TexasRed), a fluorescein dye (FITC₁₋₅-carboxy fluorescein, 6-carboxyfluorescein, fluorescein diacetate, naphthofluorescein, HEX, TET,5-carboxy JOE, 6-carboxy JOE, Oregon Green 488, Oregon Green 500, OregonGreen 514, erythrosin, eosin), a coumarin dye (7-hydroxycoumarin,7-dimethylaminocoumarin, 7-methoxycoumarin,7-amino-4-methylcoumarin-3-acetic acid or (AMCA), and Pacific Blue), acyanine (Cy) dye (Cy3, Cy3.5, Cy5, Cy5.5, Cy7), a phthalocyanine dye, aphycobiliprotein dye, (B-phycoerythrin (B-PE), R-phycoerythrin (R-PE),and allophycocyanin (APC)), a pyrene and a sulfonated pyrene, (cascadeblue), a squaraine dye, an Alexa dye (Alexa 350, Alexa 430, Alexa 488,Alexa 532, Alexa 546, Alexa 568, Alexa 594) and Lucifer yellow.

IV. Excitation Sources

A central principle of the PME technology is the discrimination of amixture of different fluorophores by the time correlation of“colorblind” fluorescence emission triggered by serially pulsingdifferent excitation lasers. This approach significantly contrasts thatof the widely used method of wavelength discrimination of fluorescenceemission, where a single excitation source, typically an argon ion laser(488 nm and 514.5 nm) excites four spectrally resolvable fluorescentdyes. The dye of this set, which emits at the longest emittingwavelength is usually the least optimally excited, which is due to poorspectral overlap between the excitation source and the dye's absorptionmaximum. This inefficient excitation has been partially overcome by theuse of fluorescence resonance energy transfer (FRET) dye-primers (Ju etal., 1995; Metzker et al, 1996) and dye-terminators (Rosenblum et al.,1997) to increase signal intensities. Obviously, the optimal method inobtaining the highest emission signal possible would be matching theexcitation source with the absorption maxima for every fluorophore inDNA sequencing assays.

The invention may use at least one laser and is flexible to accommodateas many different lasers as is feasibly possible. There may be 2, 3, 4,5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, or more lasers, depending onthe system.

A single laser may produce 1, 2, 3, 4, 5, 6, 7, 8 or more differentwavelengths for the excitation of fluorophores with different absorptionmaxima. This can be accomplished using the technique of Stimulated RamanShifting (SRS). This technique may be employed for conversion to eithershorter or longer wavelength(s). The Raman effect enables a laserfrequency to be modified by discrete increments, (the Stokes andAnti-Stokes shifts). Frequency conversion is accomplished by passinglaser light through a suitable crystal or a stainless steel cellcontaining gas at an elevated pressure, (i.e. several atmospheres).Conversion efficiency for the principal Stokes shift to longerwavelength can be as high as 35%. The nature of the crystal or gasdetermines the frequency output, for example, N₂, O₂, H₂, D₂, and CH₄give shifts of 2330 cm⁻¹, 1550 cm⁻¹, 4155 cm⁻¹, 2987 cm⁻¹, and 2917 cm⁻¹respectively, while Ba(NO₃)₂ gives a shift of 1047 cm⁻¹. A preferredRaman medium for this invention is molecular nitrogen, as 2330 cm⁻¹ isabout the desired spacing between excitation frequencies.

Until recently, gas lasers have been widely used for the excitation of“blue” and “green” fluorophores with absorption maxima ranging between488 nm and 543 nm for DNA sequencing applications. In general, theselasers include the argon ion, the krypton ion, and the helium-neon(He—Ne) lasers. These lasers are large in size, highly inefficient andrelatively expensive devices. Moreover, the lifetime of gas laser isapproximately 1,000-to-3,000 hours of use, which imposes highmaintenance cost for these instruments. Despite these disadvantages, theargon ion laser has been widely used in automated DNA sequencinginstrumentation for 15 years now (Smith et al., 1986; Probe et al.,1987) and is frequently described as the excitation source in manycapillary electrophoresis systems, see below.

On the other hand, semiconductor lasers or laser diodes are muchsmaller, lighter, and more rugged than any other laser types and havebeen employed in a wide variety of applications such as CD players,laser printers, and telecommunication systems. These compact laserstypically produce monochromatic light between 630 nm and 1100 nm. Theseextremely compact, but durable lasers can produce power in the 10-100 mWrange and have a useful lifetime of up to 100,000 hours.

The neodymium:YAG (Yttrium Aluminum Garnet) laser is the most commonsolid-state laser in use today with instruments being found in a varietyof applications such as in industry welding of heavy metals, in surgicaloperating devices, in laboratory spectroscopic equipment, or on unmannedspace probes. A solid-state laser is a source in which the active mediumis usually a transparent crystal containing a transition metal,(typically 1% or less), such as neodymium, chromium or holmium.Transitions in the metal ion are responsible for the laser's action.These lasers are optically pumped by either broadband flash-lampsources, or one or more diode laser sources. For blue and greenexcitation, solid-state lasers contain a frequency doubling or secondharmonic generating (SHG) crystal such as lithium borate or potassiumtitanyl phosphate. For example, the frequency doubled Nd:YAG laser has afundamental excitation line of 1064 nm, which is doubled by an SHGcrystal to generate green 532 nm light.

Until recently, the application of the PME technology has beenunrecognized by the lack of available and reliable solid-state lasersthat produce monochromatic light at wavelengths between 400 nm and 630nm. This emerging field, however, has recently produced solid-statelasers that generate monochromatic light at wavelengths of approximately400 nm, 473 nm, and 488 nm, which becomes suitable for DNA sequencingapplications. Thus, the development of PME is uniquely coupled to thisemerging field of laser development and well positioned to incorporatenew advances in laser technology, when available.

V. Inverse Dispersion

Because of the need for multiple laser beams incident on a singlesample, the laser beams must be steered so that they all pass through orcontact the sample. This can be accomplished by spatially combining thedifferent laser beams into one overlapping “white” beam.

Other groups have developed devices to combine two or more laser beams.Conemac (U.S. Pat. No. 6,226,126) describes a laser beam mixer having abeam combining element with a transmissive portion and a reflectiveportion. However, this technology requires that the cross sectionalshape of the second, third and so forth laser beams be distorted.Another limitation is that for each laser beam added, the combined beammust pass through an additional optical element, which introduces lossinto the system.

U.S. Pat. No. 5,991,082 discloses a lens system that forms narrowsuperimposable focal lines from multiple focal lines. This system uses aprism with multiple longitudinally arranged facets bounded by parallelridge lines and can be used to obtain a high energy radiation beam foruse in pumping an X-ray laser.

U.S. Pat. No. 6,215,598 discloses an apparatus for concentrating laserbeams, which comprises collimating devices that converge the laser beamsinto a laser beam sheet. A digital optics device shapes and concentratesthe laser beam sheet into a narrow overlapping laser beam.

In the present invention, an inverse dispersion system can be used tosteer the light from multiple lasers onto a single sample. Inversedispersion uses optical dispersion elements such as a prism assembly ora diffraction grating positioned such that light from discrete locationsis steered to be substantially colinear and/or substantially coaxialupon exiting the system. The term “substantially colinear” means thatthe laser beams or excitation lines diverge from each other at angles ofless than 5°. The term “substantially coaxial” means that the laserbeams or excitation lines diverge from each other at angles of less than5°.

The inverse dispersion system may be configured as shown in FIG. 2 inwhich five excitation lines from discrete locations are combined into asingle colinear and/or coaxial line.

High dispersion equilateral prisms constructed from high grade glass,quartz or silica are used in one preferred embodiment of the invention.The preferred orientation for the prisms relative to each other whenusing high dispersion flint glass prisms is 40°-50°, or more preferred45°. The preferred orientation for the prisms relative to each otherwhen using quartz prisms is 25°-55° or more preferred 30°-50°. Thisangle allows efficient overlap of the multiple beams by inversedispersion into a single beam. A two prism assembly is preferred,however, a single prism or an assembly with three or more prisms is alsocontemplated. Similarly, a diffraction grating such as a ruled orholographic grating can be used to combine the multiple beams. Multipleexcitation lines can be steered onto a diffraction grating such that thediffraction of the grating causes the beams to combine.

In addition to being colinear, the beams may be coaxial, with all of thelaser beams passing through the same columnar space in the sample. Thesame sample molecules will be exposed to each of the laser beamssequentially in turn as the lasers are fired.

The inverse dispersion approach uses the same principle firstdemonstrated by Sir Isaac Newton, but in reverse direction. In hisexperiment, collimated white light, from the sun, passed through anequilateral prism, and the various wavelengths became separated byangle. The beam of light passes into the prism, forming a non-zero anglewith respect to the normal to the entrance surface. According to Snell'slaw, all of the rays will be bent towards the normal as the light passesinto the more optically dense medium. Due to dispersion of the glass,the shorter wavelengths deviate more. When the rays exit the prism, allare bent a second time, but again, the shorter wavelengths bend more.The result is that the shorter wavelengths now have an angularseparation from the longer wavelengths. Blue light is deviated more thangreen, which is deviated more than yellow, and that in turn more thanred.

This process may be reversed, and that is the principle utilized forinverse dispersion. If the separated rays are made to trace paths thatare just the reverse of above, then the various wavelengths are combinedinto a single beam of “white” light. For example, light from lasers,light emitting diodes, arc lamps, incandescent lamps, etc. may becombined (after collimation and spectral filtering, if appropriate) bythis inverse dispersion method. The shorter wavelength rays or beamsenter the prism at the appropriate larger off-normal angle than thelonger wavelength beams. When the correct angles are determined fromSnell's law, the beams will all combine into a single coaxial beam. Ifdesired, the beams may be spatially offset to provide colinear beamsthat, while parallel to each other, pass through the sample at slightlydifferent positions. In the former case, the fluorescence from all ofthe beams may be imaged onto a single detector. In the latter case, thebeams may be imaged onto four or more separate detectors, or separateregions of one detector, such as a CCD camera. If the light sources arepulsed in rapid succession, the combined beam appears to be white ornearly so. If the pulsing is slow enough for the eye to follow, thecombined beam will exhibit a changing color pattern originating from thesame spatial location.

The prism is typically used at the minimum deviation angle, whereby theentering and exiting angles for a given beam are equal, or as nearly soas practical. The apex bisector will also bisect the angle formed by theentering and exiting beam. If the prism is then rotated, then these twoangles are no longer equal. This is advantageous in that it increasesboth the overall deviation angle and the amount of dispersion. However,this also causes anamorphic changes in the beam diameter. Suchanamorphic expansion can be useful if it is desirable to change a roundbeam cross section to an oblong one, or an oblong beam shape to a roundshape. If the inverse dispersion combining of beams is to be done withminimal distortion of the original beam shape, then the minimumdeviation angle is preferred.

The angular separation of the beams is increased in proportion to thenumber of prisms the beam passes through. For example, the use of twoidentical prisms doubles the angular separation. The anamorphic beamchanges can be nearly canceled by using a pair of prisms at non-minimumdeviation angles. Use of high dispersion glass, such as flint glass alsoincreases the angular separation of the incoming beams. This in turnreduces the distance needed to achieve spatial separation of theincoming beams, and provides for a more compact optical apparatus. As anexample, the present apparatus utilizes two F2 flint glass prisms.

A diffraction grating may also be used as a suitable inverse dispersionelement. For a grating exposed to a collimated beam of white light, thebeam is diffracted in accordance with the grating equation. If it is atransmission grating, the beam is diffracted away from a straight linepath, called the zero order, with the longer wavelengths deviating at alarger angle than the shorter wavelengths. The order of the dispersedwavelengths is the reverse of that for prisms. If a reflection gratingis used, again the longer wavelength beam is deviated further from thezero order reflection than a shorter wavelength. As with the prismcombiner above, beams of different wavelengths incident on the gratingin the reverse direction will provide the same sort of inversedispersion, leading to a colinearity of the beams. They may be madecoaxial if the beams are incident on the same area on the grating but atthe appropriate angles for each of the wavelengths. Conventionally ruledgratings are suitable for this purpose, however holographic gratingsgenerally exhibit less scattered light. Gratings generally can beobtained that have considerably higher dispersion than prisms, and hencedispersion angles are larger and the spacing between the light sourcescan be reduced. They are generally less efficient, so that light lossesare greater. Gratings and prisms are both sensitive to the polarizationof the light. Since the fluorescence emission is also sensitive to thedirection of the polarization, proper orientation of the electric vectorof the light should be considered. Polarization rotation devices may beadded to improve the transmission efficiency.

VI. Collection Devices

Of the possible choices for detection of fluorescence, the optimum onewill depend upon the level of fluorescence intensity. For all detectorsdescribed herein, a photon striking the detector is converted into acharge carrier, which is then detected electronically. Charge carriers,however, are generated by extrinsic processes unrelated to thefluorescence signal from a variety of sources: thermal generation,cosmic rays, and natural radioactivity. All carriers generated both fromfluorescence and from unrelated sources contribute to shot noise, awell-understood statistical phenomenon. Of the extrinsic sources ofexcess carrier noise, thermal generation of carriers is usually thedominant extrinsic noise source, which can be reduced by cooling thedetector. Fundamentally all that is needed for satisfactory detection isthat the number of charge carriers generated by fluorescence during anobservation time window is much greater than the square root of thenumber of all carriers generated during the same time interval. However,once the carriers leave the detector, the amplifying electronics willintroduce noise as well, and this electronic noise may dominate. Toavoid this situation, devices have been invented that incorporate theirown very low noise amplifiers. There are two such devices: thephotomultiplier tube (PMT) and the silicon avalanche photodiode (APD).Another approach to reducing amplifier noise is to collect carriers fora period of time and then rapidly read the collected charges out. Thismode of operation is used for photodiode array charge-coupled device(CCD) detectors.

For light levels with high enough signals that the noise generated inthe external amplifiers is negligible, the simplest device forfluorescence detection is the silicon PIN detector. This device consistsof a thin hole rich region (p) and an electron rich region (n) separatedby thick carrier deficient region (i). It is back-biased with a negativevoltage applied to the p side and a positive voltage applied to the nside. Light striking it penetrates the p region and is absorbed in the iregion generating an electron hole pair with the electron beingattracted to the n side and the hole to the p side creating a currentthrough the device. The quantum efficiency of this process is very high(˜80%). Because it is the simplest, most compact, and cheapest detector,the silicon PIN is a preferred detector. Other, more sensitive detectorsmay also be used for detecting low levels of light emission for amulti-capillary electrophoresis system and direct detection assays.

The silicon PIN detector can be made suitable for the detection of verylow light levels by introducing carrier gain into it. A photon strikesthe detector creating an electron hole pair. The electron is acceleratedby an electric field and creates additional carriers by ionization. Theadditional electrons are accelerated to produce more carriers resultingin an avalanche process and current gain. Silicon avalanche detectorsoperate in two modes analogous to that of the PMT: an analog currentmeasurement mode and a digital counting mode. When operated in theanalog mode, the current gain (˜300) is less than that of a PMT(˜10⁵-10⁶), but with exception to the lowest light levels, the signal isstill much larger than the noise in the external amplification circuit.In addition, the wavelength response range (300 to 1100 nm) of silicondetectors is much wider than any individual PMT photocathode, coveringthe fluorescent maximum of any dye that might be used for DNA sequencinginstrumentation.

Alternatively, a silicon APD can be thermoelectrically cooled andoperated in the Geiger counting mode, where individual fluorescencephotons are counted. This provides a high quantum efficiency (˜80%) withdark count levels approaching a cooled PMT (quantum efficiency typically10%). The thermoelectrically cooled silicon APD provides a compact formcombined with state-of-the-art sensitivity. While higher sensitivity maynot be required for detecting fluorescent signals from standardsequencing reactions, silicon APDs in the counting mode can be ideal fordetecting fluorescent signals directly from genomic DNA assays (i.e.,without amplification).

Detectors with the required characteristics are commercially availableand include the simple silicon PIN detector, the silicon APD, or aphotodiode array (CCD). The simple silicon detector is the cheapest, thesilicon avalanche is the most sensitive, and the CCD is most useful formultiple capillary systems as it provides many detectors in a singleunit.

VII. Coupled Systems

The PME technology has sufficient flexibility for coupling to a varietyof formats, for example, the PME system can be coupled to conventionalcapillary electrophoresis (CE) or to separation and/or purificationusing high-density arrays/biochips. Ideally, a DNA sequencing systemcapable of direct detection of fluorescent assays for genomic DNA should(i) optimally excite all fluorescent dyes, (ii) be capable ofefficiently collecting photons over a large part of the UV, visible andinfrared spectrum, (iii) continuous monitoring of fluorescent signals inhigh-throughput array or high-density formats, (iv) maximizefluorescence emission signals for detection, (v) be configured tominimize background scattered light, and be automated using replaceablegel matrices.

a. Capillary Electrophoresis

The PME fluorescence detection system of the present invention can becoupled to conventional capillary electrophoresis (CE) as a preferredmethod for resolving DNA fragments.

Microcapillary array electrophoresis generally involves the use of athin capillary or channel, which may or may not be filled with aparticular separation medium. Electrophoresis of a sample through thecapillary provides a size-based separation profile for the sample. Theuse of microcapillary electrophoresis in size separation of nucleicacids has been reported in, e.g., Woolley and Mathies (1994). The highsurface to volume ratio of these capillaries allows for the applicationof higher electric fields across the capillary without substantialthermal variation across the capillary, consequently allowing for morerapid separations. Furthermore, when combined with confocal imagingmethods, these methods provide sensitivity in the range of attomoles,which is comparable to the sensitivity of radioactive sequencingmethods. Microfabrication of microfluidic devices includingmicrocapillary electrophoretic devices has been discussed previously(e.g., Jacobsen et al., 1994; Effenhauser et al., 1994; Harrison et al.,1993; Effenhauser et al., 1993; Manz et al., 1992; and U.S. Pat. No.5,904,824). Typically, these methods comprise photolithographic etchingof micron scale channels on a silica, silicon or other crystallinesubstrate or chip, and can be readily adapted for use in the presentinvention. In some embodiments, the capillary arrays may be fabricatedfrom the same polymeric materials described for the fabrication of thebody of the device, using the injection molding techniques describedherein.

Tsuda et al., (1990), describes rectangular capillaries, an alternativeto the cylindrical capillary glass tubes. Some advantages of thesesystems are their efficient heat dissipation due to the largeheight-to-width ratio and, hence, their high surface-to-volume ratio andtheir high detection sensitivity for optical on-column detection modes.These flat separation channels have the ability to performtwo-dimensional separations, with one force being applied across theseparation channel, and with the sample zones detected by the use of amulti-channel array detector.

In many capillary electrophoresis methods, the capillaries, e.g., fusedsilica capillaries or channels etched, machined or molded into planarsubstrates, are filled with an appropriate separation/sieving matrix.Typically, a variety of sieving matrices are known in the art, which maybe used in the microcapillary arrays. Examples of such matrices include,e.g., hydroxyethyl cellulose, polyacrylamide, agarose and the like.Generally, the specific gel matrix, running buffers and runningconditions are selected to maximize the separation characteristics ofthe particular application, e.g., the size of the nucleic acidfragments, the required resolution, and the presence of native orundenatured nucleic acid molecules. For example, running buffers mayinclude denaturants, chaotropic agents such as urea or the like, todenature nucleic acids in the sample.

The use of replaceable gel matrices, which suppress electroendoosmoticflow and DNA-capillary wall interactions such as polydimethylacrylamide(Madabhushi, 1998), may be used for electrophoretic separations in thepresent invention.

b. Chromatographic Techniques

Alternatively, chromatographic techniques may be coupled to the PMEfluorescence detection system of the present invention. There are manykinds of chromatography, which may be used including liquidchromatography, HPLC and many specialized techniques, such as reversephase HPLC, normal phase HPLC, anion exchange, cation exchange,denaturing HPLC, size exclusion or gel permeation, and hydrophobicinteraction.

c. Microfluidic Techniques Microfluidic techniques can be used for fluidflow with the PME system, and includes the use of a platform such asmicrocapillaries, designed by ACLARA BioSciences Inc., or the LabChip™“liquid integrated circuits” made by Caliper Technologies Inc.Miniaturizing some of the processes involved in genetic analysis hasbeen achieved using microfluidic devices. For example, published PCTApplication No. WO 94/05414, by Northrup and White, incorporated hereinby reference, reports an integrated micro-PCR™ apparatus for collectionand amplification of nucleic acids from a specimen. U.S. Pat. No.5,304,487 to Wilding et al., and U.S. Pat. No. 5,296,375 to Kricka etal, discuss devices for collection of cell containing samples and areincorporated herein by reference. U.S. Pat. No. 5,856,174 describes anapparatus, which combines the various processing and analyticaloperations involved in nucleic acid analysis and is incorporated hereinby reference.

d. Chip Technologies

Specifically contemplated by the present inventors for combining withthe PME system are chip-based DNA technologies. These techniques involvequantitative methods for analyzing large numbers of genes rapidly andaccurately.

Chip based technologies that can be used in the current inventioninclude the those described in U.S. Pat. No. 6,153,379 and Shumaker etal. (1996) where a method of analyzing oligonucleotides is described inwhich oligonucleotides are extended with fluorescent dideoxynucleotides,and detected using an automated fluorescent DNA sequencer. Theoligonucleotide length identifies the known mutation site, and thefluorescence emission of the ddNTP identifies the mutation. Anothermethod of analyzing oligonucleotides involves using template DNAannealed to an oligonucleotide array. The analysis is done using aPhosphor Imager and alpha-³²P labels. Kurg et al., (2000) describes anintegrated system with DNA chip and template preparation, multiplexprimer extension on the array, fluorescence imaging, and data analysis.The method includes annealing DNA to immobilized primers, which promotesites for template-dependent DNA polymerase extension reactions usingfour unique fluorescently labeled dideoxy nucleotides. A mutation isdetected by a change in the color code of the primer sites.

Motorola BioChip Systems has the I-based SNP systems with arraytechnology centered on a three-dimensional gel pad format consisting offlexible content architectures.

The MassARRAY system, developed by SEQUENOM (U.S. Pat. Nos. 5,547,835,6,238,871, and 6,235,478) has a platform capable of high throughput SNPanalysis using enzymology, bioinformatics and miniaturized chip-baseddisposables with mass spectrometry detection. The MassARRAY technologycan be used to distinguish genotypes using MALDI-TOF mass spectrometry.DNA fragments associated with genetic variants are simultaneouslyseparated and detected, measuring target DNA associated with SNPs andother forms of genetic variation directly.

f. Bead Technologies

The PME system may be coupled with microbeads containing bound DNA orRNA segments. These beads may be plain or coated with material such asbiotin, terminal amines, or Protein G to facilitate binding of thebiomolecule to the bead. Microbeads may be used in conjunction with, forexample, microfluidic systems or electrophoretic systems and PMEdetection. The beads may be porous or solid and made of polymers such aspolystyrene or agarose and may optionally contain magnetic particles,such as those obtained from Dynal thus allowing use in magneticseparation techniques. The beads may also be porous thereby providingincreased surface area for binding. Magnetic beads are used in a mannersimilar to polymer beads. However, these beads contain a magnetic sourcesuch as Fe₂O₃ or Fe₃O₂ that can be used for rapid and simple separation.

VIII. Continuous Fluorescence Monitoring

To capture minute fluorescent signals for multiple capillary array orother formats derived from direct assays, the high duty cycle ofcontinuous monitoring systems has significant advantage over scanningsystems. Moreover, continuous systems have other benefits that simplifythe mechanical operation of the system, such as no moving mechanicalstages that wear down, break down, or become misaligned. These systemsuse the laser light power more efficiently allowing greater operation offluorescence excitation under photobleaching conditions. Basically,there are two known methods for continuous monitoring of fluorescentsignals, namely on-column and post-column detection. Both methods can beused with the PME technology of the current invention for DNA sequencingapplications using capillary electrophoresis.

a. On-Column Detection

The first on-column detection schemes were described using singlecapillary systems (Luckey et al., 1990; Swerdlow et al., 1990; Drossmanet al., 1990; Cohen et al., 1990). In 1990, the Smith group describedthe first 4-color on-column system using a multi-line argon-ion laser(488 nm and 514.5 nm) to illuminate a single capillary. The fluorescenceemitted from FAM, JOE, TAMRA, and ROX dye-labeled sequencing reactionswas collected orthogonal to the excitation source and using a set ofbeamsplitters, the emitted fluorescence was directed to a set of 4 PMTdetectors (Luckey et al., 1990). Karger et al. described the firston-column, spectral dispersion system using a CCD camera (Sweedler etal., 1991) to detect emission wavelengths approximately in the range of500 nm to 650 nm derived from the fluorescence of a 4-color sequencingreaction. Similar to the Smith design, the fluorescence was collectedperpendicular to the excitation path, but the authors describe theunique feature of 4 target areas that correspond to the emissionproperties of FAM, JOE, TAMRA, and ROX dye-labeled reactions and thebinning of pixels within the target areas for enhanced readout speed andreduced readout noise (Karger et al., 1991).

The first capillary array instrument was a modified DuPont GENESIS 2000DNA sequencing instrument (Probe et al., 1987), which the slab gel wasreplaced with a 12-capillary array (Zagursky et al., 1990). An argon-ionlaser beam (single line 488 nm) was scanned across the capillaries andfluorescence was detected using the 510 nm and 540 nm resolved, two PMTdetector scheme. The Mathies group has described a confocal-fluorescencesystem, which has potential for improved signal to noise and scannedback and forth using a motor-driven translation stage across a24-capillary array (Huang et al., 1992). Fluorescence was collectedusing a 180° geometry to the argon ion laser (488 nm) excitation sourceby confocal detection. Originally, a two PMT detector system coupled toa two-dye binary coding method was used with different mole fractioncombinations of FAM and JOE dye reactions to differentiate thefour-termination reaction set (Huang et al., 1992). Recently, theMathies group developed a 4-color confocal scanning detection systemthat directs the fluorescence emission through a number of differentdichroic beamsplitters to 4 PMT detectors (Kheterpal et al., 1996). The4-color confocal scanning system described here represents the coretechnology for the commercially available 96-capillary MegaBACE 1000instrument (Molecular Dynamics). More recently, the Riken group hasdescribed a 384-capillary DNA sequencer, which uses an argon ion laserin a scanning mode and splits the fluorescence emission signal to 4different band-pass filters coupled to dedicated PMT detectors (Shibataet al., 2000). Although mechanical scanning systems can uniformlyilluminate each capillary in the array, in general, they can beproblematic due to breakdown and misalignment, low duty cycle, andpotential photobleaching by duty cycle compensation with higher laserpower levels.

Several side-entry illumination schemes directly through capillaryarrays have been problematic in scaling from a single capillary to arraysystems, mainly because of reflection and refraction of the laser beamat the capillary boundaries. The Yeung group described a 10-capillarysystem that used axial beam illumination and CCD detection, in whichindividual optical fibers coupled via an argon ion laser were directlyinserted into the ends of the capillary tubes (Taylor et al., 1993). Theintrusion of optical fibers into separate capillaries, however, affectedthe electroendoosmotic flow and increased the possibility forcontamination and clogging (Lu et al., 1995). This group also describedillumination by a line of laser light focused across the array using aplano-convex cylindrical lens to illuminate a 100-capillary array (Uenoet al., 1994); however, this design inefficiently used less than 0.5% ofthe laser power to illuminate each capillary (Lu et al., 1995). Quesadaand Zhang (1996) described an 8-capillary prototype in which argon ionillumination and fluorescence detection were achieved by usingindividual optical fibers constructed in an orthogonal geometry andimaged through a spectrograph using a CCD camera. Scaling beyond theinitial individual optical fiber design, however, was reported to beproblematic because of the increased demand on laser power, and thebulkiness and irregular alignment of the optical junction connectors toeach capillary tube (Quesada et al., 1998).

To address the loss of laser illumination by refraction, two independentgroups have demonstrated that refracted laser light at the capillarysurface can be focused repeatedly under optimized optical conditions andproduce a waveguiding effect (Quesada et al., 1998; Anazawa et al.,1996). Quesada et al. (1998) demonstrated that a bi-directionallyilluminated waveguide system using an argon ion laser showed goodillumination across a 12-capillary array with a difference of less than10% across the array, and with potential for scaling to a 96-capillarysystem with near uniform illumination. Alternatively, index matching ofthe capillary array has also been shown to reduce laser light refractionand scattering across the array (Lu et al., 1995), but to a smallerdegree than waveguide illumination (Quesada et al., 1998).

b. Post-Column Detection

The first post-column detection schemes also described single capillarysystems (Swerdlow et al., 1990; Swerdlow et al., 1991). The Dovichigroup first reported a 4-color post-column detection system using asheath flow cuvette (Swerdlow et al., 1990). These authors demonstratedthe sheath flow concept using the four-spectral channel system based onthe work described by the Smith group (Luckey et al., 1990) and atwo-spectral channel system based on the work described by Prober et al.(1987). Unlike the beamsplitter design, the four-spectral channels werediscriminated using a rotating wheel containing 4 specific band-passfilters, which was synchronized to a sector wheel that alternated theexcitation source between an argon-ion laser (488 nm) and a green He—Nelaser (543.5 nm). The appropriate orientation of the filter wheeldirected the specific emission light wavelengths of FAM, JOE, TAMRA, andROX dye-labeled sequencing reactions to a single PMT detector. Thetwo-spectral channel, two intensity system used a single argon-ion laser(488 nm) to excite the 4-different succinyl-fluorescein dye-labeledreactions, which have limited spectral resolution. The emissionfluorescence centered at 510 nm and 540 nm was uniquely split using asingle dichroic mirror and detected with two PMT detectors. Theassignment of the nucleotide sequence was performed by determining theratio of baseline-corrected peak intensities (Prober et al., 1987).

The post-column sheath-flow approach has the advantage of eliminatingexcitation light scattering at the capillary surfaces and inilluminating all capillary tracks simultaneously. Kambara and Takahashidescribed the first multiple sheath-flow capillary array system using aHe−Ne laser (594 nm) and single color Texas Red (ROX) labeled DNAsequencing reactions (Kambara et al., 1993). This system was laterdeveloped into a 4-color system using the combined excitation lines fromboth an argon ion laser (488 nm) and a YAG laser (532 nm) tosimultaneously irradiate FAM, JOE, TAMRA, and ROX dye-labeled reactions.The fluorescence was dispersed using an image-splitting prism, passedthrough 4 different optical filters, and detected as two-dimensionalline images using a cooled CCD camera (Takahashi et al., 1994). TheHitachi technology described here represents the core technology for thecommercially available 96-capillary 3700 DNA sequencer instrument(Applied Biosystems).

Another application of the sheath flow approach to post-column detectionwas described in U.S. Pat. No. 6,139,800 where fluorescent detection oflabeled particles is accomplished for capillary electrophoresis.Multiple wavelength sources excite the labeled particles and multiplewavelength discriminating detectors detect the sample emissions.

Capillary array sheath-flow cuvettes require careful attention tohydrodynamic focusing, which can be achieved by uniformly spacing thecapillaries in the cuvette holder. Recently, the Dovichi group hasdescribed two sheath flow cuvettes, the rectangular cuvette that istapered to force 5-capillaries to squeeze together (Zhang et al., 1999)and the micro-machined cuvette with uniformly spaced etched grooves toalign 16 individual capillaries (Crabtree et al., 2000). Of the twodesigns, the latter one shows more promise for scaling to a 96-capillaryarray.

IX. Obtaining High Sensitivity and Low Background Scattered Light

In 1990, several groups reported limit of detection values correspondingto 10⁻¹⁹ moles for CE systems and were performed using a 10⁻¹¹ Msolution of fluorescein flowing continuously in an open capillary(Swerdlow et al., 1990; Drossman et al., 1990). These systems, however,were roughly 10-fold less sensitive than the sheath flow detectorsystem, which has a reported detection limit of 10⁻²⁰ moles (Swerdlow etal., 1990; Kambara et al., 1993). Coupled to an APD operating in theGeiger counting mode, this sheath flow system described recently by theDovichi group showed a limit of detection of 130±30 fluoresceinmolecules (Zhang et al., 1999).

The number of fluorescence counts generated is the product of twofactors: (i) the number of fluorescence photons generated and (ii) theoverall counting efficiency. The number of fluorescence photonsgenerated is given by

${Np} = {\frac{\sigma \; {NP}}{Ahv}{QYt}}$

where N is the number of dye molecules being excited, P is the laserpower (J/s), σ is the absorption cross-section (cm²), A is the area ofthe laser beam, hν is the energy of an excitation photon (J), QY is thequantum yield for fluorescence, and t is the observation time (s). Theoverall counting efficiency is given by

${Eff} = \frac{{SA} \cdot {QE}}{4\; \pi}$

where SA is the solid angle of fluorescent light collection (insteradians) and QE is the quantum efficiency of the detector. Assumingthat the cross-section is 3.8×10⁻¹⁶ cm² (ε=100,000 liters/(mol-cm)), thewavelength of the excitation is 600 nm, the QY is unity, the numericalaperture is unity, and the quantum efficiency is 0.8, then

${Np} = {73\frac{NPt}{A}}$

The PME system of the current invention is useful as a DNA sequencingdevice for analyzing SNPs directly from genomic DNA without cloning orPCR amplification. Estimating 106 white blood cells per cm³ of blood,one calculates 73,000 counts in a second could be expected for a singleSNP probing of 1 ml of blood without any concentration of solution witha laser power of 1 mW and an area of 1 cm². Concentration would reduce Awithout reducing N. Thus, there is an easily detectable signal withoutelectrophoresis or heroic measures, granted that the sequencing assaysare free of unincorporated dye. Note that focusing the laser reduces N,but simultaneously reduces A by the same factor so that the signal doesnot depend upon focusing as long as the numerical aperture can bemaintained (defocusing limit) or the dye is not destroyed by two photonabsorption effects (tight focusing limit).

The situation is somewhat different when determining a number of SNPssimultaneously. Then electrophoresis becomes necessary in order toseparate the various fragments. Typically in Sanger sequencing, a10-to-30 μL sample is introduced into the 3700 DNA sequencinginstrument, but only about 10 nL is actually introduced into thecapillary. This is a loss in N of about a factor of 1000-to-3000reducing N to ˜100-to-300. However, if using the sheath flow approach(Anazawa et al., 1996; Zhang et al., 1999), the dye-tagged fragmentsemerging from a 50 μm ID capillary will occupy a cylinder about 2 mmlong and perhaps 100 μm in diameter. Its cross-sectional area A will be2×10⁻³ cm² and the number of counts in a 1 s counting interval will be

${{Np} = {{73\frac{300 \cdot 0.001 \cdot 1}{0.002}} = 11}},000$

This calculation is consistent with the report by Zhang et al. (1999)that 130 fluorescein molecules emerging from a 50 μm capillary could bedetected in 0.2 sec counting time. It will be possible to reduce thewastage factor of 3000 cited above to perhaps 100 by devising low volumemethodologies to use a 1 μL sample.

Thus, a capillary electrophoresis system that utilizes multiple, compactsolid-state lasers and laser diodes coupled to highly efficientdetection devices, which employ continuous illumination and sheath flowdetection features is a preferred embodiment of the current invention.These integrated technologies are well suited for the application of thePME technology and have sufficient feasibility for direct detectionassays.

X. Single Nucleotide Polymorphisms (SNPS)

Spontaneous mutations that arise during the course of evolution in thegenomes of organisms are often not immediately transmitted throughoutall of the members of the species, thereby creating polymorphic allelesthat co-exist in the species populations. Often polymorphisms are thecause of genetic diseases. Several classes of polymorphisms have beenidentified. For example, variable nucleotide tandem repeats (VNTRs) arepolymorphic and arise from spontaneous tandem duplications of di- ortrinucleotide repeated motifs of nucleotides. If such variations alterthe lengths of DNA fragments generated by restriction endonucleasecleavage, the variations are referred to as restriction fragment lengthpolymorphisms (RFLPs). RFLPs are been widely used in human and animalgenetic analyses and forensic and paternity testing.

Another class of polymorphisms is generated by the replacement of asingle nucleotide. Such single nucleotide polymorphisms (SNPs) rarelyresult in changes in a restriction endonuclease site. SNPs are the mostcommon genetic variations and occur once every 300-to-1000 bases, andseveral SNP mutations have been found that affect a single nucleotide ina protein-encoding gene in a manner sufficient to actually cause agenetic disease. SNP diseases are exemplified by hemophilia, sickle-cellanemia, hereditary hemochromatosis, late-onset Alzheimer disease, etc.

SNPs can be the result of deletions, point mutations and insertions andin general any single base alteration, whatever the cause, can result ina SNP. The greater frequency of SNPs means that they can be more readilyidentified than the other classes of polymorphisms. The greateruniformity of their distribution permits the identification of SNPs“nearer” to a particular trait of interest. The combined effect of thesetwo attributes makes SNPs extremely valuable. For example, if aparticular trait reflects a mutation at a particular locus, then anypolymorphism that is linked to the particular locus can be used topredict the probability that an individual will be exhibit that trait.

Several methods have been developed which can be combined with PMEtechnology to screen polymorphisms and some non-limiting examples arelisted below. Such methods include the direct or indirect sequencing ofthe site, the use of restriction enzymes where the respective alleles ofthe site create or destroy a restriction site, the use ofallele-specific hybridization probes, the use of antibodies that arespecific for the proteins encoded by the different alleles of thepolymorphism, or any other biochemical interpretation.

a. DNA Sequencing

Traditionally, DNA sequencing has been accomplished by the“dideoxy-mediated chain termination method,” also known as the “SangerMethod” (Sanger, F., et al., 1975), which involves the chain terminationof DNA synthesis by the incorporation of 2′,3′-dideoxynucleotides(ddNTPs) using DNA polymerase. The reaction also includes the natural2′-deoxynucleotides (dNTPs), which extend the DNA chain by DNAsynthesis.

Thus, balanced appropriately, competition between chain extension andchain termination results in the generation of a set of nested DNAfragments, which are uniformly distributed over thousands of bases anddiffer in size as base pair increments. Electrophoresis is used toresolve the nested set of DNA fragments by their respective size. Thefragments are then detected by the previous attachment of four differentfluorophores to the four bases of DNA (i.e., A, C, G, and T), whichfluoresce at their respective emission wavelengths after excitation attheir respective excitation wavelengths using PME technology. The DNAsequencer may be based on an electrophoresis system with the throughputcapacity of a single column, 4, 8, 16, 48, 96 or 384-capillaryinstrument or may integrate with other separation platforms, includinghigh-density chip arrays.

Similar methods which can be used with PME technology include the“chemical degradation method,” also known as the “Maxam-Gilbert method”(Maxam, A. M., et al., 1977). Sequencing in combination with genomicsequence-specific amplification technologies, such as the polymerasechain reaction may be utilized to facilitate the recovery of the desiredgenes (Mullis, K. et al., 1986; European Patent Appln. 50,424; EuropeanPatent Appln. 84,796, European Patent Application 258,017, EuropeanPatent Appln. 237,362; European Patent Appln. 201,184; U.S. Pat. No.4,683,202; U.S. Pat. No. 4,582,788; and U.S. Pat. No. 4,683,194).

b. Primer Extensions Methods for SNP Detection

A preferred assay for the detection of multiple SNPs is the singlenucleotide primer extension method, which has also been called singlenucleotide incorporation assay and primer-guided nucleotideincorporation assay. These methods rely on the specific hybridization ofan identically complementary oligonucleotide sequence to the geneticregion or target of interest, which has been amplified by the polymerasechain reaction (PCR) or cloned using standard molecular biologytechniques (Sambrook et al., 1989). However, unlike the Sanger reaction,the primer extension method is assayed using either single unlabeled orlabeled dNTPs, 3′-modified-dNTPs, base-modified-dNTPs, oralpha-thio-dNTPs or a mixture of ddNTPs, which all can chain terminateDNA synthesis under appropriate conditions following the incorporationof a single nucleotide (U.S. Pat. Nos. 4,656,127; 5,846,710; 5,888,819;6,004,744; 6,013,431; 6,153,379, herein incorporated by references).Here, the word usage of 2′-deoxynucleoside triphosphate,2′-deoxyribonucleoside triphosphate, dNTP, 2′-deoxynucleotide,2′-deoxyribonucleotide, nucleotide or natural nucleotide are used assynonymous terms and used interchangeably in the current patentdocument.

1. Using Single Unlabeled dNTPs

A method, called pyrosequencing, uses singly added unlabeled dNTPs andis based on a repetitive cyclic method of start-stop DNA synthesis ofsingle nucleotide addition. Pyrosequencing is a mini-sequencingtechnique and relies on a multi-enzyme cascade to generate light byluciferase as the mode of detection (Nyren et al., 1993; Ronaghi et al.,1998). PCR amplified DNA fragments, which contain a 5′-biotin group areimmobilized on streptavidin-coated magnetic beads. An incorporatedunlabeled nucleotide event is monitored by the release of inorganicpyrophosphate and the subsequent release of light following the primerextension step. Because pyrosequencing is a cyclic DNA sequencingstrategy, the placement of the oligonucleotide immediately adjacent tothe 5′-position is not always required, and the primer can be placedwithin the sequencing read-length of the method, usually 20 bases. Majordisadvantages with the pyrosequencing technique are the method has lowsensitivity, the high cost of the reagents, particularly the enzymes,and sequence difficulties with homopolymer repeats (i.e., AAAAA) andhigh “GC” rich regions.

2. Using Single Labeled dNTPs

Unlike the pyrosequencing method, which can extend the primer beyond asingle nucleotide position, other investigators have reported singlenucleotide incorporation assays using single nucleotides labeled withradioactive, non-radioactive, or fluorescent tags (Sokolov, 1990;Syvanen et al., 1990; Kuppuswamy et al., 1991; Prezant and Ghodsian,1992). In these strategies, the placement of the oligonucleotide isimmediately adjacent to the 5′-position of the single nucleotidemutation site under investigation. Sokolov showed the specificincorporation and correct identification of single nucleotide sequencesof a known sequence in the cystic fibrosis gene using alpha ³²P-dCTP andalpha ³²P-dGTP (Sokolov, 1990). In another report, a similar approachwas described for the detection of the Δ508 mutation in the cysticfibrosis gene and point mutations in exon 8 of the factor IX gene(Hemophilia B) (Kuppuswamy et al., 1991). Following PCR amplification ofspecific target regions, specific oligonucleotides, which hybridizedimmediately adjacent to the 5′-position of the mutation underinvestigation, were extended by one nucleotide using single alpha³²P-dNTPs. Moreover, a dual labeling strategy for SNP detection wasreported for exon 4 of the apolipoprotein E gene using differentcombinations of ³H-labeled dTTP, alpha ³²P-labeled dCTP, ordigoxigenin-11-dUTP. Following immobilization of PCR-amplified fragmentson avidin-coated polystyrene beads, single nucleotide extension assayswere performed and incorporated nucleotides were detected using a liquidscintillation counter at different window settings for ³H and ³²Pradioactivity or colorimetrically using an alkaline phosphatase assay(Syvanen et al., 1990). A similar method, called Trapped-OligonucleotideNucleotide Incorporation (TONI) using a biotinylated primer immobilizedon streptavidin magnetic beads and singly added alpha ³²P-labeled dNTPswas described for genetic screening of mitochondrial polymorphisms anddifferent hemoglobin genotypes (Prezant and Ghodsian, 1992).

3. Using Single 3′-Modified dNTPs

Metzker et al. proposed the base addition sequencing strategy (BASS),which is a mini-sequencing technique and involves stepwise singlenucleotide sequencing by repetitive cycles of incorporation of3′-O-modified nucleotides, detection of the incorporated nucleotide, anddeprotection of the 3′-O-modified nucleotide to generate the 3′-OHsubstrate and allow for the next cycle of DNA synthesis (Metzker et al.,1994). Eight different 3′-O-modified dNTPs were synthesized and testedfor incorporation activity by a variety of DNA polymerases.3′-O-(2-Nitrobenzyl)-dATP is a UV sensitive nucleotide and was shown tobe incorporated by several thermostable DNA polymerases. Base specifictermination and efficient photolytic removal of the 3′-protecting groupwas demonstrated. Following deprotection, DNA synthesis was reinitiatedby the incorporation of natural nucleotides into DNA. The identificationof this labile terminator and the demonstration of a one-cyclestop-start DNA synthesis identified the initial steps in the developmentof a novel sequencing strategy. The major challenge for SNP detectionusing BASS, however, is the continued synthesis and identification ofnovel 3′-modified nucleotides that give the desired properties oftermination with removable protecting groups.

4. Using Single Base-Modified 3′-dNTPs

Kornher and Livak (1989) described another method by incorporatingmobility shifting modified-dNTPs (i.e., the attachment of a biotin groupor a fluorescein group to the base) into a PCR amplified DNA sample. TheSNP is identified by denaturing gel electrophoresis by observing a“slower” migrating band, which corresponds to the incorporated modifiednucleotide into the DNA fragment.

5. Using Single alpha-thio-dNTPs

Other methods that can be employed to determine the identity of anucleotide present at a polymorphic site utilize modifiedalpha-thio-dNTPs, which are resistant to exonuclease cleavage (U.S. Pat.No. 4,656,127). An oligonucleotide, of identical sequence to acomplementary target region, immediately flanks the 5′-position of thesingle nucleotide mutation site under investigation. If the polymorphicsite on the DNA contains a nucleotide that is complementary to theparticular exonuclease-resistant nucleotide derivative present, thenthat derivative will be incorporated by a polymerase and extend theoligonucleotide by one base. Such incorporation makes the primerresistant to exonuclease cleavage and thereby permits its detection. Asthe identity of the exonuclease-resistant nucleotide derivative is knownone can determine the specific nucleotide present in the polymorphicsite of the DNA.

6. Using Single Labeled 2′,3′-dideoxynucleotides

Several groups have reported methods for single nucleotide incorporationassays using labeled 2′,3′-dideoxynucleotides to specifically assaygiven SNPs of interest, which are detected by autoradiography,calorimetrically, or fluorescently (Lee and Anvret, 1991; Livak andHainer, 1994; Nikiforov et al., 1994; Shumaker et al., 1996). All ofthese methods rely on PCR to amplify genomic DNA from patient materialand careful design of oligonucleotide sequences to target specific knownmutations in different genes. The separation of dideoxynucleotideincorporated DNA fragments can be achieved electrophoretically (Lee andAnvret, 1991; Livak and Hainer, 1994; Nikiforov et al., 1994; Shumakeret al., 1996) or by using high-density array chip formats (Shumaker etal., 1996).

7. By Direct Detection from Genomic DNA

One aspect of this invention is to develop a DNA sequencing device foranalyzing SNPs directly from genomic DNA without cloning or PCRamplification. The present invention circumvents the problems associatedwith the previously described methods for SNP detection, which rely on aprior PCR or cloning step. These steps potentially add errors in samplehandling, introduction of exogenous contamination, significant costs inreagents and labor and seriously hamper the introduction ofhigh-throughput SNP detection into a clinical or medical setting.Because of its simplicity, the PME technology has the capability ofgreatly increasing the multiplexing of numerous SNPs simultaneously,which is significantly limited in other previously described systems.For example, 4-, 8-, 12- and 16-different fluorophores identified hereincan be coupled to appropriate ribonucleotides, 2′-deoxynucleotides,2′,3′-dideoxynucleotides, 2′3′-unsaturated-dNTPs and/or other modifiednucleotides.

Moreover, the assay can be multiplexed, and coupled to a high-throughputelectrophoresis system, and in this configuration, it has the capabilityof analyzing 2,000-to-4,000 independent SNPs in approximately 30-to-60minutes. Multiplexing is accomplished by varying the length of thespecific primers by increments of 2-to-3 bases, and by increasing thenumber of fluorophores detected in the SNP assay. Twenty to 100, or morespecifically 30-to-50 primers, all differing in length, could be assayedin a single nucleotide primer extension assay, which could be resolvedby electrophoresis and detected by PME in a single capillary. Since thelongest primer sequence will generally not exceed 100 bases in length,fast separation times are expected. It is noteworthy that SNP specificprimers can also be arrayed in a high-density chip format, thuseliminating the need for electrophoresis. The scalability of the DNAsequencer is multiplied by 96-capillaries.

c. Massively Parallel Signature Sequencing (MPSS) Strategy

Brenner et al. (2000) recently presented data on their massivelyparallel signature sequencing (MPSS) strategy, which is another cyclicprocess involving type II restriction digestion/ligation/hybridizationto sequence over 269,000 signatures of 16-20 bases in length (Brenner etal., 2000). The main disadvantage of MPSS is low efficiency where only25% of the starting DNA templates yield signatures after application ofthe base-calling algorithms.

d. Ligase Chain Reaction (LCR)

LCR can also amplify short DNA regions of interest by iterative cyclesof denaturation and annealing/ligation steps (Barany, 1991). LCRutilizes four primers, two adjacent ones that specifically hybridize toone strand of target DNA and a complementary set of adjacent primersthat hybridize to the opposite strand. LCR primers must contain a 5′-endphosphate group such that thermostable ligase (Barany, 1991) can jointhe 3′-end hydroxyl group of the upstream primer to the 5′-end phosphategroup of the downstream primer. Successful ligations of adjacent primerscan subsequently act as the LCR template resulting in an exponentialamplification of the target region. LCR is well suited for the detectionof SNPs since a single-nucleotide mismatch at the 3′-end of the upstreamprimer will not ligate and amplify, thus discriminating it from thecorrect base. Any or all of the LCR primers can be labeled withdifferent fluorescent dyes for unambiguous discrimination of specificSNPs. Although LCR is generally not quantitative, linear amplificationsusing one set of adjacent primers, called the Ligase Detection Reaction,can be quantitative. Coupled to PCR, linear ligation assays can also beused as a mutation detection system for the identification of SNPs usingboth wild-type-specific and mutant-specific primers in separatereactions.

e. Oligonucleotide Ligation Assay (OLA)

The Oligonucleotide Ligation Assay was first reported to detect SNPsfrom both cloned and clinical materials using a 5′-end biotin groupattached to the upstream primer and a nonisotopic label attached to thedownstream primer (Landegren et al., 1988). Allele-specifichybridizations and ligations can be separated by immobilization to astreptavidin-coated solid support and directly imaged under appropriateconditions without the need for gel electrophoretic analysis.Subsequently, Nickerson et al. have described an automated PCR/OLAmethod for the diagnosis of several common genetic diseases. FollowingPCR amplification, the upstream 5′-end biotinylated primer anddigoxigenin labeled downstream primer are ligated together underappropriate and specific annealing conditions, captured on streptavidincoated microtiter plates and detected calorimetrically by an alkalinephosphatase assay (Nickerson et al., 1990)

f. Ligase/Polymerase-Mediated Genetic Bit Analysis

U.S. Pat. No. 5,952,174 describes a method that also involves twoprimers capable of hybridizing to abutting sequences of a targetmolecule. The hybridized product is formed on a solid support to whichthe target is immobilized. Here the hybridization occurs such that theprimers are separated from one another by a space of a singlenucleotide. Incubating this hybridized product in the presence of apolymerase, a ligase, and a nucleoside triphosphate mixture containingat least one deoxynucleoside triphosphate allows the ligation of anypair of abutting hybridized oligonucleotides. Addition of a ligaseresults in two events required to generate a signal, that is extensionand ligation. This provides a higher specificity and lower “noise” thanmethods using either extension or ligation alone and unlike thepolymerase-based assays, this method enhances the specificity of thepolymerase step by combining it with a second hybridization and aligation step for a signal to be attached to the solid phase.

XI. Data Acquisition and Analysis

The PME system, including switching the lasers and collecting the dataare under computer control in a unified hardware/software framework.Cross-platform versatility is achieved, for example, by using PCI-busdata acquisition and controller cards and LabView™ software fromNational Instruments. The graphically oriented acquisition and analysisenvironment provided by LabView has led to its widespread adoption inlaboratory use. Software programs have been developed to perform severaloperations for the PME sequencing prototypes including: (i) generating atrigger signal for the TTL clock chip to govern the basic 4 sub-cycles(serial pulsing of lasers 1 through 4) of each cycle, (ii) controllingthe blocking of scattered light, (iii) acquisition of thetime-integrated signals from the photodetector, and (iv) controllingvarious operations for automated capillary electrophoresis methods.Scattered light is controlled by use of a liquid crystal tunable filterunder electronic command (e.g., the VariSpec from CRI, Inc.) to providea different edge block for each of the four lasers. When using a PMT oravalanche photodiode, sampling should be taken several times persub-cycle for purposes of time-integration. For the full-scalemultichannel CCD operation, only one read per sub-cycle is necessary.These different modes of operation are easily handled in software. Asmentioned above, a primary goal of this invention is direct detection,which would eliminate the need for PCR amplification. This requires highdirect sensitivity such as can be obtained with a spectroscopic-gradeCCD camera with very low readout noise (e.g., a few accumulated photonsper readout).

In addition, software programs that perform a number of data analysissteps, including spectral matrix correction, baseline correction,electrophoretic mobility corrections, base-calling of the singlenucleotide, quantitation of peak heights for heterozygote analyses,allele association by electrophoretic position and order of differentfluorescently labeled gene targeted primers are developed. Excitation byPME produces some level of cross-talk from the non-matched laser pulsesother than from the best matched laser. As discussed previously,laser-dye combinations that minimize non-matched laser cross-talk can beeasily identified, so that time correlated excitation of the correctfluorophore can be identified and made with high confidence. In general,however, it will be necessary to accommodate heterozygous base pairs,particularly for SNP analyses in which more than one fluorophore isexcited at a time. Under non-saturating conditions, this leads to linearrelations between the number N_(i) of photons detected due toillumination by laser i and the number n_(j) of molecules of dye j,

N_(i)=Σ_(j)α_(i,j)n_(j)

The matrix α implicitly contains factors including the molar extinctioncoefficients of the different dyes at frequency i, their quantum yields,the efficiencies of the laser and the detection system, and attenuationeffects. From a practical point of view, the relative magnitudes of theelements α_(i,j) are calibrated experimentally. The matching of the dyemaxima to the laser colors makes the matrix diagonally dominant,allowing it to be inverted without numerical difficulties. The inversionof α removes the residual cross-talk between the dyes. Thus it should bepossible to directly obtain the relative numbers of dye molecules withmaximum contrast from the four-color experiments. Corrections to thismay come from scattered light. While a simple baseline correction iseasily accommodated, light fluctuations will add some noise to theexperiments. Several full cycles of the four lasers will pass duringeach elution component, allowing reduction of the noise by signalaveraging. At the same time, the quantification of the noise provides areal-time diagnostic for estimating confidence levels on the signalmeasurements. Base-calls should in any case proceed with high confidencesince the precise handling of the cross-talk will ordinarily yield onedye population that is much higher than the others. In those cases whereheterozygotes are present, it is straightforward to distinguish thesemixed-populations since they will yield two dyes with higher (andapproximately equal) populations.

As used herein, the term “timing program” is meant to include eithersoftware or hardware configured to signal a laser firing sequence. Thetiming program will also contain information from the laser firingsequence, which can be correlated with the fluorescence emission signal.

As used herein, the term “excitation line” means a laser beam or outputfrom another excitation source having a spectral wavelength or itscorresponding frequency.

As used herein, the term “substantially all” means at least 90%. Forexample, “substantially all of the fluorescence signal” is at least 90%of the signal.

As used herein, the term “substantially corresponds” means that thedifference between the two is less than 5%. For differences inwavelengths in the visible spectrum, this corresponds to differences of20-33 nm, or more preferably 10-20 nm, or even more preferably 5-10 nm,or most preferably, when the absorption maxima of a dye “substantiallycorresponds” to the excitation wavelength of an excitation line, the twowavelengths are less than 5 nm.

As used herein, the term “optically matched” means that the wavelengthmaxima are within one nm of each other.

The term “substantially colinear” means that the laser beams orexcitation lines diverge from each other at angles of less than 5°.

The term “substantially coaxial” means that the laser beams orexcitation lines diverge from each other at angles of less than 5°.

The term “phased shifted,” means that the phase relationship between twoalternating quantities of the same frequency is changed. For example,consider two trains of repeating pulses such as pulse train (1) laser 1on followed by laser 1 off for three times as long and pulse train (2)laser 2 on followed by laser 2 off for three times as long. One wouldsay that the sequence of equal time periods of laser 1 on, laser 1 off,laser 2 on, laser 2 off corresponds to the sum of pulse train (1) andpulse train (2) with the phase of pulse train (2) delayed by a phaseshift of 180° or a half cycle. Note that for 180°, delayed or advancedphase shifts are equivalent.

As used herein, the term an “on-time window” is defined as the window oftime corresponding to when the excitation line is incident on the sampleand includes the window of time corresponding to the time after theexcitation line has ceased firing and before a second excitation line isincident on the sample.

As used herein the specification, “a” or “an” may mean one or more. Asused herein in the claim(s), when used in conjunction with the word“comprising”, the words “a” or “an” may mean one or more than one. Asused herein “another” may mean at least a second or more.

XII. Examples

The following example is included to demonstrate preferred embodimentsof the invention. It should be appreciated by those of skill in the artthat the techniques disclosed in the examples which follow, representtechniques discovered by the inventor to function well in the practiceof the invention, and thus can be considered to constitute preferredmodes for its practice. However, those of skill in the art should, inlight of the present disclosure, appreciate that many changes can bemade in the specific embodiments which are disclosed and still obtain alike or similar result without departing from the spirit and scope ofthe invention.

Example 1 Optical System

To test the concept of the PME system, a simple breadboard device wasbuilt to test the feasibility of discriminating different fluorescentsignals from a mixture of two BODIPY fluorophores (Metzker et al.,1996). The optical path for combining the pulsed 532 nm and 635 nm linesis depicted schematically in FIG. 1 as solid lines. The laser lightemitted from the green 532 nm solid state, diode-pumped,frequency-doubled Nd:YAG laser (Intelite, Minden, N.Y.) and the red 635nm SPMT diode laser module with external potentiometer (Blue SkyResearch, San Jose, Calif.) were each directed using two commercialgrade aluminum steering mirrors (Edmund Industrial Optics, Barrington,N.J.) to a dual prism assembly. The prisms were coated with a singlelayer HEBBAR antireflection material, which reduced polarization at theprism surfaces by increasing total transmittance. The high dispersionequilateral prisms were constructed from F2, grade “A” fine annealedflint glass and were positioned at a forty-five degree angle relative toone another to allow efficient overlap of the two beams by inversedispersion into a single beam, FIG. 2. The flexibility of this designallows as many as eight excitation lines originating from discrete pointsources (five lasers are shown in FIG. 1 for illustration) to becombined efficiently by the inverse dispersion strategy.

The combined laser beams were directed into the cuvette assembly box,which consists of a hollow aluminum lightproof box. The box was modifiedby affixing two “floating” adjustable iris fixtures (Edmund IndustrialOptics) to minimize the amount of stray light entering the box. A 10 cmcylindrical optically correct glass cuvette (NSG Precision Cells, Inc,Farmingdale, N.Y.) was installed and mounted using two black delrinholders. A 500K multi-alkali PMT detector, which has good sensitivity inthe range of 280 nm to 850 nm, was coupled to the cuvette assembly box.The fluorescence was detected directly from the cuvette using acollection lens in an orthogonal geometry to the propagation directionof the excitation laser beams.

Example 2 Pulse Generation System

There are a number of methods to serially pulse multiple lasers,including mechanical chopping and TTL control. One strategy was toserially pulse the 532 nm solid-state laser and the 635 nm diode laserby TTL control using 74174-clock chip, (FIG. 3). The advantages of theclock chip TTL circuit are its simplicity and flexibility as it isdesigned to pulse of up to eight discrete sources. As an alternative, aTTL bucket brigade circuit was constructed because of its simplisticdesign in pulsing 4-lasers using 2 dual J/K flip/flop chips. The TTLClock Chip essentially provides a means for distributing the timingpulses from a master clock on the computer to the appropriate lasers. Aseach clock pulse is received, the chip output sequentially shifts onestep from Q0 to Q1 . . . and finally to Q7 on the 8th clock pulse. Eachlaser is turned on in turn for one and only one clock pulse. The totalcycle time may be easily varied by several orders of magnitude, fromtens of seconds to milliseconds simply by changing the master clockfrequency, and this has been successfully tested. The duration of thelaser pulses are always identical to each other, and the off timebetween the pulses remain in the same exact proportion to each other, sothe overall cycle time may be changed with a single parameter.

Example 3 Results and Discussion from the 2 Color PME Study

A preliminary experiment was performed to determine the feasibility ofthe PME approach to discriminate each fluorophore from a mixture offluorescence dyes. To test the concept of “colorblind” detection, thisexperiment was performed without the aid of fluorescence band passfilters, laser line blocking filters, gratings, prisms, or any otherdispersing elements to aid in distinguishing one dye's emission from theother. Moreover, the raw output from the photomultiplier was sentdirectly to an oscilloscope, without signal averaging or any other typeof processing enhancement. Each laser was alternately pulsed for 1.2msec and was configured with the red laser connected to Q0 and the greenlaser connected to Q3, FIG. 3. Altering the green laser to Q2 gave thecorrect firing sequence, which verified the proper configuration of theTTL circuit (data not shown). The remaining Q inputs were idle andresulted in dark spacing between laser pulses of 2.4 msec (red-to-green)and of 4.8 msec (green-to-red). The red and green lasers provided 5.5 mWand 4 mW of power, respectively. The difference in power settings waspurposeful to partially offset the higher detector sensitivity of thegreen fluorescence over the red fluorescence. Photographs were taken bya digital camera in real time, and the fluorescent signals were recordedin a downward (negative) direction, as the PMT multiplies electrons.

The two dyes examined were BODIPY (523/547) and BODIPY (630/650), whichhave narrow absorption/emission half-bandwidths (Metzker et al., 1996),and therefore are ideal for the color-blind PME detection scheme. Thedyes were analyzed at a concentration of approximately 10⁻⁵ M inethanol. This moderately high concentration was chosen to assure thatthe signals were derived entirely from the dye solutions, and not fromother sources, such as stray light, thus providing an accurate measureof the contrast ratio. The emission from each dye fell in toto onto thered-sensitive photomultiplier, which is a key feature of the color-blindmethodology.

In FIG. 4A, the oscilloscope trace was obtained from an equal mixture ofBODIPY dyes in the cuvette. The two channels from the oscilloscopephotographs were set to record the trigger signal, which turns on thered laser (upper trace) and the fluorescence signal from the PMTdetector (lower trace). The green laser pulse was subjected to a partialmodulation, which gives the fluorescence output a “two-finger”appearance, making it easily distinguishable from the smooth red laserfluorescence. The small variation observed in the red laserpulse-to-pulse fluorescence intensity was due to 120 Hz leakage from aninadequately rectified AC power supply, and can be corrected byinsertion of a capacitor π filter in the power supply in theexperimental section. As shown, the timing of the sequential firing ofthe red laser and then the green laser resulted in significantfluorescence signals when both BODIPY dyes were present in solution.

FIG. 4B shows the total fluorescence signal from the serial pulsing ofthe green and red lasers with only the BODIPY 630/650 (red dye) presentin the cuvette. Whereas the large fluorescence signal is time correlatedwith the firing of the red laser, the green laser only imparts a small“cross-talk” signal to the red dye. This cross-talk was measured to beapproximately 4% of the red laser signal, which is attributed to thehighly efficient coupling of a laser precisely matched to the red dyeabsorption peak and the narrower absorption spectral properties ofBODIPY dyes. Both aspects give the desired low excitation efficiency ofthe off-resonant green laser. This result clearly illustrates goodcontrast between laser excitations for the same dye using the PMEapproach. Since the ratio of red to green excitation efficiency can bedetermined, a cross-talk matrix can be computed and mathematicallyapplied to yield a much higher contrast ratio.

FIG. 4C shows the total fluorescence signal from the serial pulsing ofthe red and green lasers with only the BODIPY 523/547 (green dye)present in the cuvette. The only fluorescence signal observed is timecorrelated with the firing of the green laser, which gives the“two-finger” signature. Unlike that of the BODIPY 630/650, thecross-talk signal observed from the red laser is negligible on thisscale, and further signal amplification revealed it to be considerablyless than 1% of that from the green laser. This observation is expectedbecause longer wavelength excitation sources should not impose photonabsorption on shorter wavelength dyes (i.e., the red laser does notexcite the green dye). This feature illustrates an important and keyadvantage of reduced cross-talk of fluorophores using the PME strategy.Consider a four dye system, which is made-up of blue, green, yellow, andred dyes. The blue dye should not exhibit cross-talk from the sequentialfiring of the green, yellow, and red lasers. The green dye, on the otherhand, will exhibit cross-talk from the only blue laser, but not theyellow or red lasers. The yellow dye will exhibit cross-talk from theblue and green lasers, but not the red laser and so forth. In otherwords, the observed cross-talk on the “blue” portion of the spectrumrelative to the absorption/excitation maxima of a given dye is negated,which is significantly different from emission cross-talk of blue green,yellow, and red dyes excited using a single excitation source.

An excellent contrast ratio for the discrimination of two differentBODIPY dyes using the PME technology by detecting all of thefluorescence emission in a true color-blind fashion is demonstrated. Theexperiment was designed using no spectral filtering elements of anykind, and the signal was taken directly from the oscilloscope in realtime without signal averaging or other processing. These data show thatthe choice of experimental conditions provided significant fluorescencesignal for which scattered laser light signals are negligible.Therefore, the 25:1 contrast ratio observed for this unaveraged rawsignal obtained with laser pulses on the msec timescale provides agenuine comparison of the time correlated fluorescence detectiontechnique.

Prophetic Example 4 Development of a 1-capillary 4-Color PME Prototype

a. Develop 4-Color: Identification of the Optimal 4 Laser-DyeCombination

Six different solid-state lasers and/or laser diode modules have beenidentified with excitation wavelengths that match the absorption maximaof a number of commercially available fluorophores, most of which havebeen used for DNA sequencing. Other lasers and fluorophores can also beidentified by comparing and matching the excitation maxima of thefluorophore with the emission wavelength of the laser. Candidate dyesshould show good quantum yields and have narrow absorption spectra. Thenon-limiting list of dyes listed herein below initially meet theserequirements, although other commercially available fluorophores andlasers may be tested as well. For experimentation purposes, each dye iscoupled to the universal sequencing primer (5′-TTGTAAAACGACGGCCAGT)(Metzker et al., 1996) (Sequence ID No.1) as representative oftermination products for the SNP assay.

TABLE 1 Laser Fluorophore Blue 399 nm solid state,7-dimethylaminocoumarin (409/473), indium gallium cascade blue(396/410), and 7- nitride laser hydroxycoumarin (386/448). Blue 473 nmor 488 nm 5-carboxyfluorescein (494/518), 1,3,5,7- solid state, diode-tetramethyl-BODIPY (495/503), Oregon pumped, frequency-doubled green 488(496/524), and the 5,7-dimethyl- Nd: YAG laser BODIPY (503/512).* Green532 nm solid BODIPY (523/547) (536/554 when coupled state, diode-pumped,to a primer) frequency-doubled Nd: YAG laser Yellow 594 nm He—Ne BODIPY589/617 and BODIPY 581/591 (592/603 when coupled to a primer) Red 635 nmSPMT diode BODIPY 630/650 (643/651 when coupled laser module with to aprimer) external potentiometer Red 670 nm SPMT diode The BODIPY(650/665) dye (661/667 when laser module with coupled to a primer) andcyanine 5 dye external potentiometer

Although some dyes listed in Table 1 have a listed absorption maxima onthe blue side of the excitation source, these dyes will be consideredfor use since the attachment of dyes to DNA usually results in a redshift in the absorption/emission spectra. The absorption/emission valuesfor the dyes given in parenthesis correspond to the absorption andemission wavelengths when coupled to a universal sequencing primer.

A systematic evaluation of each laser-dye combination will be comparedfor good excitation characteristics and between laser-dye pairs toidentify an optimal set of 4 laser-dyes for DNA sequencing applications.Each laser will be set-up, similar to the green and red laser experimentand pulsed using the TTL clock chip for excitation and cross-talkexperiments as described in Example 3. It is anticipated that numerousnew solid-state lasers and laser diodes and new fluorescent dyes willcontinue to be developed and commercialized with unique emissionwavelengths ranging below 400 nm to beyond 1100 nm that can be used inthe current invention. Due to the modular configuration of the PMEsystem, the testing of additional laser-dye pairs is straightforward.

b. Construction of the 1-Capillary Breadboard Prototype

A 1-capillary electrophoresis unit will be set-up on a breadboardplatform, and the electrophoresis will be driven initially using a 30 kVpower supply. A Plexiglas box equipped with a safety interlock will beconstructed to enclose the samples and the running buffers. Initially,electrophoresis will be performed under ambient conditions due to thenature of the short primer extension products; however, a temperaturecontrolled heating jacket to improve electrophoretic resolution will beconstructed if necessary. The separation format will use fused silicacapillaries (150 μM OD, 50 μM ID, and 50 cm in length), POP-6 solutionas the separation matrix, and TBE as the running buffer. A 1-capillarysheath flow cuvette will be constructed using the rectangular, tapereddesign described by Zhang et al. (1999) and sheath flow will be drivenby syringe pump at a flow rate of approximately 0.3 mL per hour.

c. Sensitivity Experiments for Direct Detection

Although limited sensitivity information can be obtained from the2-color PME system (FIG. 1), more data will be obtained from conductingsensitivity experiments directly using the 1-capillary instrument.Subsequent to the identification of the 4 laser-dye set, but overlappingwith the construction of the 1-capillary instrument, the PME lasersystem will be coupled to the electrophoresis device. For limit ofdetection assays, both the PMT and the silicon APD (current and countingmodes) will be investigated over a wide range of fluorophore-labeleduniversal primer concentrations. Sensitivity assays will be conductedusing free zone and POP-6-based capillary electrophoresis. A uniquefeature of the PME system is that limit of detection experiments will beperformed for the 4 laser-dye sets identified previously. It should benoted that limit of detection experiments are only informative regardingsensitivity when the test dye is optimally excited and producing maximumfluorescence signal. Sensitivity experiments are not possible orpractical using all four fluorophores with the standard spectrallyresolved DNA sequencing systems because the longer wavelength dyes areinefficiently excited. Therefore, the limit of detection experimentstypically published in the literature are performed using the dye mostclosely matched to the laser source (out of the set of four), which isusually fluorescein and the argon ion laser (Swerdlow et al., 1990;Drossman et al., 1990; Swerdlow et al., 1990; Zhang et al., 1999). Here,limit of detection experiments will be performed using all four PMEfluorophores because the lasers are closely matched for optimalexcitation and therefore will produce a more robust picture forsensitivity with respect to the entire sequencing chemistry.

d. Development of Rapid Sample Preparation Methods for DirectFluorescent Assays from Genomic DNA

The PME instrument should be able to detect as few as 10⁴-to-10⁵fluorescent molecules. Given that 1 mL of whole blood containsapproximately 10⁶ white blood cells, direct detection (without the needfor amplification of the sample) of multiple SNPs is possible.Initially, SNP assays will be performed using standard PCR techniquesand diluted appropriately to simulate direct genomic DNA levels. Thisapproach will allow the performance of limit of detection experimentswithout dependence or delay for the development of optimized samplepreparation methods and direct genomic SNP assays.

Sample preparation methods will be developed from whole blood to befast, simple, and amenable to direct single nucleotide primer extensionassays. Typically, most methods involve the fractionation of whole bloodinto serum, red blood cells, and white blood cells, of which the latteris used for analysis. Sample preparation experiments can rely oncommercially available kits and published protocols for evaluation andoptimization.

As discussed hereinabove, sequencing assays are typically performed inμL quantities, but loaded onto commercial capillary electrophoresisinstruments in nL quantities. To minimize wasting direct assay samples,reaction volume assays will be optimized in a target volume of 1 μL.Since electrokinetic injection will be implemented as the injectionmethod for each prototype, injection biases will most likely occurdepended on sample purity (Huang et al., 1988). Therefore, severalsolid-phase and affinity-based purification schemes will be investigatedfor producing highly purified fluorescently labeled SNP assays, whichare devoid of contaminants, such as unincorporated fluorescentterminators, salts, and other electro-competing macromolecules.

In the event that the sensitivity limit of the PME technology is severalorders of magnitude higher than anticipated (i.e., 10⁶-to-10⁷fluorescent molecules), direct detection from whole blood can still beachieved. This can be done by increasing the amount of blood analyzedfrom 1-to-10 mL, and/or performing a linear amplification of the primerextension assay by temperature cycling, typically used in Sangersequencing reactions.

Prophetic Example 5 Construction of a Portable 8-Capillary PME DNASequencer

a. Construction of 8-APD detector for a Portable System

A PME DNA sequencer that is portable will be useful for any applicationswhere there are space limitations or where it is important to be able tomove the sequencer. The technology to modify the PME DNA sequencer suchthat it is portable is currently available. For the portable DNAsequencer, the optical system developed for the breadboard will beadapted to become more compact and robust. The highly efficient dualprism combiner will be initially adapted to the portable sequencer.Constructed with microbench components, the optics train will beincorporated into a 4-rail structure, which was developed for the veryrigid needs of laser cavity mirror supports. The commercially availableminiature 4-rail system will also be used to support the sheath flowcuvette and collection optics. As previously discussed, commercial diodelaser modules are remarkably compact, typically 1″ or 2″ long, and aregenerally available with optical fiber coupled outputs. Fibersplitter/combiners have been developed for laser based communications,and contingent on this rapidly emerging technology, it may be feasibleto combine the beams and deliver the 4-laser sources to the sheath flowcuvette in a single optical fiber. For this design, only a conventionalachromatic lens will be needed to project the collimated alternatingmulticolor beam through the sheath flow cuvette.

A wide field f/1 (NA ˜0.5) lens will be used to collect the fluorescentlight from the capillary plumes and project it onto 8 APDs. A microscopeobjective is often used for this purpose, but may suffer vignetting andconsequent loss of fluorescence signal from the outermost capillaryplumes. The lens mount will be equipped with opposing adjustment screwsthat lock the lens into place after optimization. The light path will beshielded with baffles to reduce scattered laser light reaching thedetectors. An optional liquid crystal device will be used as an edgefilter to block scattered laser light, as needed; this device has arejection ratio of about 4 orders of magnitude. Unlike the familiarrotating filter wheel, the liquid crystal device has no mechanicalmoving parts. The liquid crystal filter has a response time of severalmilliseconds, so that it will be cycled under computer control alongwith the 4 lasers, blocking scattered light from each one in turn, whilepassing essentially all of the fluorescent light to the color blind APDdetectors.

Although it is preferable to imaged fluorescent light directly onto theAPDs, the collection lens, which typically magnifies the image 20× maynot be enough to resolve 8 images for detection. One solution is to usea small mirror or prism affixed to each APD housing, which can deflectthe beam at right angles. This design can be mounted in a staggeredarray and thereby reduce this congestion. Individual gradient refractiveindex (GRIN) lenses and optical fiber couplings to each APD will also beconsidered in the portable configuration. However, the insertion lossfor a properly coated beam steering prism is about 2%, and it is mostunlikely that the fiber coupling will perform as well. This fibercoupling problem is much more significant for the projected fluorescentimage, which behaves as an extended source, than it is for a laser beam.Finally, the same rigid 4-rail structure mentioned above will be used tosupport the detection system.

The laser and TTL circuit power supplies typically have a footprint of afew square inches, and the power supplies for the APDs and the 10 kVelectrophoresis modules are slightly larger, but still only a few incheslong. These various electronic components will be easily positionedbeneath and around the capillaries, which will travel around theperimeter of the system, thus avoiding sharp bends.

b. PME of Residual Signal

Residual fluorescence may be detected immediately after very shortexcitation laser pulses have irradiated the sample. With such anapproach, the lasers will be off during the period that the fluorescentsignal is collected. This may be particularly important for thedevelopment of sequencing on a chip, because the chip almost inevitablywill generate large amounts of scattered light.

Specifically the intent is to sequentially fire pico-second laser pulsesat a fluorescently labeled DNA sample and then “look” for a fluorescentresponse on the nanosecond time-scale, immediately after the laser pulseends. This novel approach is a logical extension to the centralprinciple of operation intrinsic to the core PME technology. Thisinnovative experimental strategy is referred to as “Looking In The Dark”or “PME-LITD”.

The primary advantage of the Looking In The Dark strategy is thecomplete elimination of scattered light, which at low levels offluorescence is likely to be a main source of noise in the PMEinstrument. This technique, if successful, could have enormousimplications for improving the signal-to-noise ratio and potentiallyimprove the overall sensitivity of the instrument.

The following example details a simple sequence of events to illustratethe PME-LITD concept:

-   -   1. The first laser in sequence is pulsed for 50 pico-seconds.    -   2. A 500 pico-second time delay is applied after the laser has        been switched off.    -   Note that during the delay period no fluorescence is sampled by        the detector.    -   3. A fast photon counter is used to look for any fluorescent        response from the labeled DNA during the ensuing 50 nano-second        gated window.    -   4. Steps 1 through 3 are repeated in sequence for each laser in        the subcycle.    -   5. The pico-second pulsed excitation and nano-second gated        detection windows cycle continuously.

For a four color system, the above steps would generate a subcycle timethat is 202.2 nanoseconds. This implies that over an eight second timewindow, (approximate time for a labeled DNA band to pass through an ABI3700 cuvette), around 40 million complete subcycles would be completed.The data collected will then be appropriately averaged and furtherprocessed to yield high quality analyzed data.

To conduct these types of experiments, lasers that are capable ofgenerating very short pulses of sub-nanosecond duration will berequired. Pico-second laser sources are commercially available from anumber of companies including Coherent Laser Group, Newport, andPicoQuant. For example, Coherent has a diode pumped mode-locked laserwith fundamental wavelengths at either 1047 nm, 1053 nm or 1064 nm,which generates pulses as short as 2 ps. The second harmonics can easilybe generated from picosecond sources, hence the following wavelengthswould be available: 532 nm, 526.5 nm, and 523.5 nm. Newport alsomanufactures a “NanoLaser” that generates sub-nanosecond green, (532 nm)light, at an average power of more than 6 mW.

In addition, an instrument that is capable of counting photons on asub-nanosecond time scale will also be needed; such devices areavailable from a variety of manufacturers. For example, “FAST ComTec”produces a single photon counting instrument, which has resolution onthe time-scale of 500 pico-seconds. Becker & Hickl GmbH alsomanufactures a four channel correlated single photon counting devicethat has resolution down to 813 femto-seconds. Furthermore, it should benoted that when coupled into an appropriately configured electroniccircuit the recovery time of a silicon avalanche photo-diode detector,(following illumination by scattered light from a excitation laserpulse), is of the order of 500 pico-seconds. This rapid recovery timewill permit the effective observation of fluorescence from a dye with afluorescent lifetime of several nanoseconds in the complete absence ofany laser excitation, i.e. “in the dark”.

Four wavelengths can be generated from a single laser, as opposed tousing four synchronized and mode-locked lasers. This can be done usingStimulated Raman Shifting, (SRS).

An experiment to test the PME-LITD strategy comprises a simple two-colorsystem. Specifically, a mode-locked Nd:YAG laser generating 50pico-second pulses will be coupled to a Raman cell filled with molecularnitrogen. The superimposed multi-wavelength output from the Raman cellwill be then dispersed and ultimately recombined using a four-prismassembly. In the middle of the four-prism assembly, (i.e. where thevarious excitation lines are separated and traveling approximately inparallel), a pair of electro-optic modulators will be used to chop thecolored pulses—selecting alternate pulses from each beam. The recombinedbeams will then be directed into a cuvette assembly—similar to theprototype described in FIG. 1. Finally, the time-resolved fluorescencewill be detected using a fast photon counter that looks for photons in awindow that spans the range from 0.5 ns-50.5 ns after the cessation ofeach laser pulse.

c. Construction of a 96-Capillary PME Suitcase DNA Sequencer

A portable 96-capillary PME DNA sequencer is envisioned as an aspect ofthe current invention. In one embodiment, the four-laser illuminationsystem described in the 8-capillary sheath flow cuvette system will beused for the 96 capillary system. All four alternating excitation lineswill be coaxial and well collimated to facilitate the illumination ofthe 96 fluorescent plumes. Although the compact multi-laser source willremain unchanged, it will not be practical to scale the detection systemfrom 8 APDs to 96 discrete detectors. A CCD camera, however, will bemore suited to perform this operation. A fast lens such as f/1, withgood imaging quality will be installed for efficient light collection. Asecond lens will be used to re-image the light onto the CCD. Thecomputer-controlled liquid crystal filter may be interposed between thetwo lenses to block scattered laser light, if needed. Baffles will beused to minimize stray light, but there are no restricting aperturesthat reduce the wide cone angle of collection, or dispersing elementsthat further attenuate the signal.

Essentially all of the fluorescent light from one sheath flow plume willfall on one particular group of pixels, and these pixels are binnedtogether so they are read out as a single unit, which will reducereadout noise. Binning of all of the fluorescence from a capillary intoeffectively one giant pixel provides a single robust signal from eachcapillary plume even when the amount of fluorescing dye is quite small.

The CCD camera is quite compact, and even with adding thermoelectriccooling to reduce background noise, fitting the CCD detector into acompact device will not be problematic. A portable computer will readout the CCD contents at the end of each laser pulse. For a standardvideo rate of 30 Hz, the entire cycle frequency of 4 lasers will be 7.5Hz (5 Hz with the incorporation of a liquid crystal laser blocker), andthis will allow for the data from dozens of readout cycles to be signalaveraged per one elution event. Following the construction of the CCDsuitcase system, detailed limit of detection experiments will beperformed to compare it to the performance of the 8-capillary APDsuitcase prototype.

All of the methods disclosed and claimed herein can be made and executedwithout undue experimentation in light of the present disclosure. Whilethe compositions and methods of this invention have been described interms of preferred embodiments, it will be apparent to those of skill inthe art that variations may be applied to the methods and in the stepsor in the sequence of steps of the method described herein withoutdeparting from the concept, spirit and scope of the invention. Morespecifically, it will be apparent that certain agents which are bothchemically and physiologically related may be substituted for the agentsdescribed herein while the same or similar results would be achieved.All such similar substitutes and modifications apparent to those skilledin the art are deemed to be within the spirit, scope and concept of theinvention as defined by the appended claims.

REFERENCES

The following references, to the extent that they provide exemplaryprocedural or other details supplementary to those set forth herein, arespecifically incorporated herein by reference.

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1. A method of identifying sample components comprising: (a) obtaining abiological sample; (b) labeling said sample with one or morefluorophores; (c) separating components of said sample; and (d)detecting said sample components with a device wherein said devicecomprises: one or more lasers configured to emit two or more excitationlines, each excitation line having a different excitation wavelength; atiming circuit coupled to the one or more lasers and configured to firethe two or more excitation lines sequentially according to a timingprogram to produce time-correlated fluorescence emission signals fromthe sample; and a non-dispersive detector positioned to collect thetime-correlated fluorescence emission signals; wherein said detectorcollects time correlated data from said sample comprising fluorescentemissions of the sample as a result of irradiation by the one or moreexcitation lines.
 2. The method of claim 1, wherein said samplecomponents are nucleic acids.
 3. The method of claim 1, wherein saidsample components are amino acids.
 4. The method of claim 1, whereinsaid sample components are proteins.
 5. The method of claim 1, whereinsaid separating is by electrophoresis.
 6. The method of claim 1, whereinsaid separating is by chromatography.
 7. The method of claim 1, whereinsaid separating is by mass spectrometry.
 8. The method of claim 1,wherein said sample components are addressed on high density chiparrays.
 9. The method of claim 1, further comprising: (e) contactingsaid sample components on a surface comprising immobilizedoligonucleotides at known locations on said surface; and (f) performinga single nucleotide incorporation assay.
 10. The method of claim 1,further comprising: (e) contacting said sample components on a surfacecomprising immobilized oligonucleotides at known locations on saidsurface; and (f) performing a mini-sequencing assay.
 11. The method ofclaim 9, further comprising rastering said surface or said excitationlines such that said excitation lines contact said surface at multiplelocations.